Systems and methods for biochemical analysis including a base instrument and a removable cartridge

ABSTRACT

Systems and methods for conducting designated reactions utilizing a base instrument and a removable cartridge. The removable cartridge includes a fluidic network that receives and fluidically directs a biological sample to conduct the designated reactions. The removable cartridge also includes a flow-control valve that is operably coupled to the fluidic network and is movable relative to the fluidic network to control flow of the biological sample therethrough. The removable cartridge is configured to separably engage a base instrument. The base instrument includes a valve actuator that engages the flow-control valve of the removable cartridge. A detection assembly held by at least one of the removable cartridge or the base instrument may be used to detect the designated reactions.

RELATED APPLICATIONS

This application is a continuation of U.S. application Ser. No.15/313,643 filed on Nov. 23, 2016, which is a national stage entry ofPCT Application No. PCT/US2015/032545, entitled “SYSTEMS AND METHODS FORBIOCHEMICAL ANALYSIS INCLUDING A BASE INSTRUMENT AND A REMOVABLECARTRIDGE”, filed on May 27, 2015, which claims priority to U.S.Provisional Application No. 62/003,264 filed on May 27, 2014. Each ofthe foregoing applications is hereby incorporated by reference in itsentirety.

BACKGROUND

Embodiments of the present application relate generally to systems andmethods for conducting biochemical reactions and, more particularly, tosystems and methods in which a base instrument interacts with aremovable cartridge to conduct reactions for at least one of samplepreparation or biochemical analysis.

Various biochemical protocols involve performing a large number ofcontrolled reactions on support surfaces or within designated reactionchambers. The controlled reactions may be conducted to analyze abiological sample or to prepare the biological sample for subsequentanalysis. The analysis may identify or reveal properties of chemicalsinvolved in the reactions. For example, in a cyclic-array sequencingassay (e.g., sequencing-by-synthesis (SBS)), a dense array of DNAfeatures (e.g., template nucleic acids) are sequenced through iterativecycles of enzymatic manipulation. After each cycle, an image may becaptured and subsequently analyzed with other images to determine asequence of the DNA features. In another biochemical assay, an unknownanalyte having an identifiable label (e.g., fluorescent label) may beexposed to an array of known probes that have predetermined addresseswithin the array. Observing chemical reactions that occur between theprobes and the unknown analyte may help identify or reveal properties ofthe analyte.

There has been a general demand for systems that automatically performassays, such as those described above, in which the system requires lesswork by, or involvement with, the user. Presently, most platformsrequire a user to separately prepare the biological sample prior toloading the biological sample into a system for analysis. It may bedesirable for a user to load one or more biological samples into thesystem, select an assay for execution by the system, and have resultsfrom the analysis within a predetermined period of time, such as a dayor less. At least some systems used today are not capable of executingcertain protocols, such as whole genome sequencing, that provide datahaving a sufficient level of quality and within a certain cost range.

BRIEF DESCRIPTION

In an embodiment, a system is provided that includes a removablecartridge having a cartridge housing. The removable cartridge alsoincludes a fluidic network that is disposed within the cartridgehousing. The fluidic network is configured to receive and fluidicallydirect a biological sample to conduct at least one of sample analysis orsample preparation. The removable cartridge also includes a flow-controlvalve that is operably coupled to the fluidic network and is movablerelative to the fluidic network to control flow of the biological sampletherethrough. The cartridge housing includes a housing side that definesan exterior of the removable cartridge and permits operative access tothe flow-control valve. The system also includes a base instrumenthaving a control side that is configured to separably engage the housingside of the removable cartridge. The housing and control sidescollectively define a system interface. The base instrument includes avalve actuator that engages the flow-control valve through the systeminterface. The removable cartridge also includes a detection assemblythat is held by at least one of the removable cartridge or the baseinstrument. The detection assembly includes an imaging detector and areaction chamber that is in flow communication with the fluidic network.The imaging detector is configured to detect designated reactions withinthe reaction chamber.

In an embodiment, a method of sequencing nucleic acids is provided. Themethod includes providing a removable cartridge having a cartridgehousing, a fluidic network disposed within the cartridge housing, and aflow-control valve that is operably coupled to the fluidic network andmovable relative to the fluidic network. The cartridge housing includesa housing side that defines an exterior of the removable cartridge. Themethod also includes contacting the removable cartridge to a baseinstrument. The housing side of the removable cartridge separablyengages a control side of the base instrument to collectively define asystem interface. The base instrument includes a valve actuator thatengages the flow-control valve through the system interface. The methodalso includes fluidically directing a biological sample to flow throughthe fluidic network of the cartridge to conduct at least one of sampleanalysis or sample preparation in the cartridge. The biological sampleis directed to flow into a reaction chamber, wherein the flow of thebiological sample is controlled by action of the valve actuator on theflow-control valve. The method also includes detecting the biologicalsample using an imaging detector directed to the reaction chamber,wherein the detection assembly is held by at least one of the removablecartridge or the base instrument.

In an embodiment, a removable cartridge is provided that includes acartridge housing having a sample port that opens to an exterior of thecartridge housing and is configured to receive a biological sample. Thecartridge housing has an array of electrical contacts and a mechanicalinterface that are exposed to the exterior. The cartridge housing isconfigured to be removably coupled to a base instrument. The removablecartridge may also include a fluidic network having a plurality ofchannels, a reaction chamber, and a storage module. The storage moduleincludes a plurality of reservoirs for storing reagents. The fluidicnetwork is configured to direct reagents from the reservoirs to thereaction chamber, wherein the mechanical interface is movable relativeto the fluidic network to control flow of fluid through the fluidicnetwork. The system also includes an imaging device disposed within thecartridge housing and positioned to detect designated reactions withinthe reaction chamber. The imaging device is electrically coupled to thearray of electrical contacts for communicating with the base instrument.The mechanical interface may be configured to be moved by a baseinstrument when the removable cartridge is coupled to the baseinstrument.

In an embodiment, a removable cartridge is provided that includes acartridge housing having a sample port that opens to an exterior of thecartridge housing and is configured to receive a biological sample. Theremovable cartridge may also include a rotatable valve that is disposedwithin the cartridge housing. The rotatable valve has a fluidic side anda plurality of valve ports that open at the fluidic side. The rotatablevalve has at least one flow channel extending between the valve ports,wherein the rotatable valve is rotatable between different rotationalpositions. The removable cartridge may also include a microfluidic bodyhaving a body side that is slidably coupled to the fluidic side of therotatable valve. The microfluidic body may at least partially define afluidic network that includes a sample channel in flow communicationwith the sample port. The sample channel has a network port that opensto the body side of the microfluidic body. The fluidic network may alsoinclude a reservoir configured to hold a reagent. The reservoir is inflow communication with a reservoir port that opens to the fluidic sideof the microfluidic body. The fluidic network also includes a feedchannel in flow communication with a reaction chamber of the fluidicnetwork. The feed channel has a feed port that opens to the body side ofthe microfluidic body. The rotatable valve is configured to rotatebetween first and second rotational positions. The network port isfluidically coupled to the feed port through the rotatable valve whenthe rotatable valve is in the first rotational position. The reservoirport is fluidically coupled to the feed port through the rotatable valvewhen the rotatable valve is in the second rotational position.

In an embodiment, a removable cartridge is provided that includes acartridge housing having a sample port that opens to an exterior of thecartridge housing and is configured to receive a biological sample. Thecartridge housing may include a mating side that is configured to faceand removably couple to a base instrument. The removable cartridge alsoincludes a fluidic network that is disposed within the housing. Thefluidic network includes a sample channel that is in flow communicationwith the sample port. The removable cartridge also includes a channelvalve having a flex member that is configured to move between first andsecond positions. The flex member blocks flow through the sample channelwhen in the first position and permits flow through the sample channelwhen in the second position. The mating side of the cartridge housingincludes an access opening that exposes the channel valve to theexterior of the cartridge housing. The access opening is configured toreceive a valve actuator of the base instrument for moving the flexmember between the first and second positions.

In an embodiment, a base instrument is provided that includes a systemhousing having a mating side that is configured to engage a removablecartridge. The base instrument also includes a rotating motor that isconfigured to engage a rotatable valve of the removable cartridge. Thebase instrument also includes a valve actuator that is configured toengage a channel valve of the removable cartridge and an array ofelectrical contacts configured to electrically couple to the removablecartridge. The base instrument also includes a system controller that isconfigured to control the rotating motor and the actuator to perform anassay protocol within the removable cartridge. The system controller isconfigured to receive imaging data from the removable cartridge throughthe array of electrical contacts. Optionally, the base instrumentincludes a thermal block for heating a portion of the removablecartridge.

In an embodiment, a removable cartridge is provided that includes acartridge housing having a sample port that opens to an exterior of thecartridge housing and is configured to receive a biological sample. Thecartridge housing includes a mating side that is configured to face andremovably couple to a base instrument. The removable cartridge alsoincludes a microfluidic body disposed within the cartridge housing. Themicrofluidic body has a body side and includes a fluidic network. Thefluidic network has a plurality of discrete channels and correspondingports that open at the body side at a valve-receiving area. Theremovable cartridge also includes a rotatable valve disposed within thecartridge housing. The rotatable valve has a fluidic side and at leastone flow channel that extends between a plurality of valve ports. Thevalve ports open to the fluidic side. The fluidic side is rotatablycoupled to the valve-receiving area of the body side of the microfluidicbody, wherein the rotatable valve is movable between differentrotational positions to fluidically couple the discrete channels. Therotatable valve has a mechanical interface that is accessible along themating side and configured to engage the base instrument such that therotatable valve is controlled by the base instrument.

In an embodiment, a removable cartridge is provided that includes acartridge housing having a sample port that opens to an exterior of thecartridge housing and is configured to receive a biological sample. Thecartridge housing has a mating side that is configured to removablycouple to a base instrument. The removable cartridge also includes amicrofluidic structure that is disposed within the cartridge housing andincludes a plurality of stacked printed circuit board (PCB) layers. ThePCB layers include fluidic layers that define channels and a reactionchamber when the PCB layers are stacked. The PCB layers also include awiring layer. The removable cartridge also includes a CMOS imager thatis configured to be mounted to the microfluidic structure andelectrically coupled to the conductive wiring layer. The CMOS imager isoriented to detect designated reactions within the reaction chamber.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1A is a schematic diagram of a system formed in accordance with anembodiment that is configured to conduct at least one of biochemicalanalysis or sample preparation.

FIG. 1B is a flow chart illustrating a method of conducting designatedreactions for at least one of sample preparation or sample analysis.

FIG. 2 is a schematic diagram of a system formed in accordance with anembodiment that is configured to conduct at least one of biochemicalanalysis or sample preparation.

FIG. 3 is a side view of a system formed in accordance with anembodiment that includes a base instrument and a removable cartridge.

FIG. 4 is a top-down view of a system formed in accordance with anembodiment that includes a base instrument and a removable cartridge.

FIG. 5 is a cross-section of a portion of a system formed in accordancewith an embodiment illustrating a flow-control valve having a firstposition.

FIG. 6 is a cross-section of a portion of the system of FIG. 5illustrating the flow-control valve having a second position.

FIG. 7 is a cross-section of a portion of a system formed in accordancewith an embodiment illustrating a flow-control valve having a firstposition.

FIG. 8 is a cross-section of a portion of the system of FIG. 5illustrating the flow-control valve having a second position.

FIG. 9 is a cross-section of a portion of a system formed in accordancewith an embodiment illustrating a flow-control valve having a firstposition.

FIG. 10 is a cross-section of a portion of the system of FIG. 5illustrating the flow-control valve having a second position.

FIG. 11 is a perspective view of an exposed portion of a removablecartridge formed in accordance with an embodiment.

FIG. 12 is a cross-section of a rotatable valve that may be used withthe removable cartridge of FIG. 11 .

FIG. 13 illustrates an arrangement of ports that may be fluidicallyinterconnected using the rotatable valve.

FIG. 14 illustrates a flow diagram of an example of a method of using aflexible printed circuit board (PCB) and roll-2-roll (R2R) printedelectronics for the monolithic integration of CMOS technology anddigital fluidics.

FIG. 15 illustrates an exploded view of an example of a fluidics stackhaving certain layers that can be laminated and bonded together usingthe method of FIG. 16 .

FIG. 16 illustrates a perspective view of an example of a CMOS devicethat can be integrated into the fluidics layers of a microfluidiccartridge using the method of FIG. 14 .

FIGS. 17A, 17B, 18, 19, and 20 illustrate side views of a structure andshowing an example of a process of attaching a CMOS device to a flexiblePCB using the method of FIG. 14 .

FIG. 21 illustrates a side view of an example of a structure formedusing the method of FIG. 14 , wherein the fluidics layers and a CMOSdevice are integrated together in a microfluidic cartridge.

FIGS. 22A and 22B illustrate perspective views of an example of amembrane valve, wherein membrane valves can be integrated into thefluidics layers.

FIGS. 23A and 23B illustrate cross-sectional views of the membrane valvein the open and closed states, respectively.

FIG. 24 illustrates a schematic diagram of an example of a microfluidiccartridge that includes both CMOS technology and digital fluidicsintegrated together.

FIGS. 25 and 26 illustrate perspective views of a microfluidic cartridgeassembly, which is one example of the physical instantiation of theintegrated microfluidic cartridge shown in FIG. 24 .

FIGS. 27A and 27B illustrate perspective views of an example of afluidics assembly that is installed in the microfluidic cartridgeassembly shown in FIGS. 25 and 26 .

FIGS. 28A and 28B illustrate a plan view and a cross-sectional view,respectively, of an example of a heater trace that can be installed inthe fluidics assembly shown in FIGS. 27A and 27B.

FIGS. 29, 30, 31, 32, 33A and 33B illustrate various other views of themicrofluidic cartridge assembly of FIG. 25 , showing more detailsthereof.

FIGS. 34 through 42 illustrate a process of deconstructing of themicrofluidic cartridge assembly of FIG. 25 as a means to reveal theinterior components thereof.

FIG. 43 shows a transparent perspective view of a portion of themicrofluidic cartridge assembly of FIG. 25 and showing the variousreagent fluid reservoirs and sample loading ports thereof.

FIG. 44 shows another transparent perspective view of a portion of themicrofluidic cartridge assembly of FIG. 25 and further showing thefluidics channels thereof.

FIG. 45 shows a cross-sectional view of the microfluidic cartridgeassembly of FIG. 25 , which shows more details thereof.

FIGS. 46A, 46B, 47A, 47B, and 48 show various views of the housing ofthe microfluidic cartridge assembly of FIG. 25 , which shows moredetails thereof.

FIGS. 49, 50, 51A, 51B, and 52 show various views of the base plate ofthe microfluidic cartridge assembly of FIG. 25 , which shows moredetails thereof.

FIGS. 53A and 53B illustrate other perspective views of the fluidicsassembly of the microfluidic cartridge assembly showing more detailsthereof.

FIGS. 54A, 54B, and 54C illustrate other views showing more details ofthe flexible PCB heater of the fluidics assembly of the microfluidiccartridge assembly.

FIGS. 55A and 55B show a perspective view and plan view, respectively,of the inlet/outlet ports layer of the fluidics layers shown in FIG. 15and FIG. 27 .

FIGS. 56A and 56B show a perspective view and plan view, respectively,of the fluidics channels layer of the fluidics layers shown in FIG. 15and FIG. 27 .

FIGS. 57A and 57B show a perspective view and plan view, respectively,of the flexible PCB layer of the fluidics layers shown in FIG. 15 andFIG. 27 .

FIGS. 58A and 58B show a perspective view and plan view, respectively,of the sequencing chamber bottom layer of the fluidics layers shown inFIG. 15 and FIG. 27 .

FIGS. 59A and 59B show a perspective view and plan view, respectively,of the sequencing chamber layer of the fluidics layers shown in FIG. 15and FIG. 27 .

FIGS. 60A and 60B show a perspective view and plan view, respectively,of the membrane layer and the sequencing chamber top layer of thefluidics layers shown in FIG. 15 and FIG. 27 .

FIGS. 61A and 61B illustrate a flow diagram of an example of a method ofusing the microfluidic cartridge assembly to perform multiplex PCR anddownstream mixing needed for sequencing.

FIG. 62 illustrates a side view of an example of a CMOS flow cell,wherein up to about 100% of the biosensor active area is accessible forreagent delivery and illumination.

FIG. 63 illustrates an exploded view of an example of one instantiationof the CMOS flow cell shown in FIG. 49 .

FIGS. 64 and 65 illustrate a perspective view and a side view,respectively, of the CMOS flow cell shown in FIG. 63 when fullyassembled.

FIG. 66 illustrates perspective views of an example of the flow cell lidof the CMOS flow cell shown in FIGS. 63, 64, and 65 .

FIGS. 67, 68, 69, and 70 illustrate an example of a process of providingan extended planar surface in the CMOS flow cell, upon which the flowcell lid may be mounted.

FIGS. 71A, 71B, 71C, and 71D illustrate another example of a process ofproviding an extended planar surface in the CMOS flow cell, upon whichthe flow cell lid may be mounted.

FIGS. 72, 73, 74, and 75 illustrate yet another example of a process ofproviding an extended planar surface in the CMOS flow cell, upon whichthe flow cell lid may be mounted.

DETAILED DESCRIPTION

Embodiments set forth herein may be used to perform designated reactionsfor sample preparation and/or biochemical analysis. The term“biochemical analysis” may include at least one of biological analysisor chemical analysis. FIG. 1A is a schematic diagram of a system 100that is configured to conduct biochemical analysis and/or samplepreparation. The system 100 includes a base instrument 102 and aremovable cartridge 104 that is configured to separably engage the baseinstrument 102. The base instrument 102 and the removable cartridge 104may be configured to interact with each other to transport a biologicalsample to different locations within the system 100, to conductdesignated reactions that include the biological sample in order toprepare the biological sample for subsequent analysis, and, optionally,to detect one or more events with the biological sample. The events maybe indicative of a designated reaction with the biological sample. Insome embodiments, the removable cartridge 104 is similar to theintegrated microfluidic cartridge 1100 (shown in FIG. 24 ) or themicrofluidic cartridge assembly 1200 (shown in FIGS. 25 and 26 ).

Although the following is with reference to the base instrument 102 andthe removable cartridge 104 as shown in FIG. 1A, it is understood thatthe base instrument 102 and the removable cartridge 104 illustrate onlyone exemplary embodiment of the system 100 and that other embodimentsexist. For example, the base instrument 102 and the removable cartridge104 include various components and features that, collectively, executea number of operations for preparing the biological sample and/oranalyzing the biological sample. In the illustrated embodiment, each ofthe base instrument 102 and the removable cartridge 104 are capable ofperforming certain functions. It is understood, however, that the baseinstrument 102 and the removable cartridge 104 may perform differentfunctions and/or may share such functions. For example, in theillustrated embodiment, the removable cartridge 104 is configured todetect the designated reactions using an imaging device. In alternativeembodiments, the base instrument 102 may include the imaging device. Asanother example, in the illustrated embodiment, the base instrument 102is a “dry” instrument that does not provide, receive, or exchangeliquids with the removable cartridge 104. In alternative embodiments,the base instrument 102 may provide, for example, reagents or otherliquids to the removable cartridge 104 that are subsequently consumed(e.g., used in designated reactions) by the removable cartridge 104.

As used herein, the biological sample may include one or more biologicalor chemical substances, such as nucleosides, nucleic acids,polynucleotides, oligonucleotides, proteins, enzymes, polypeptides,antibodies, antigens, ligands, receptors, polysaccharides,carbohydrates, polyphosphates, nanopores, organelles, lipid layers,cells, tissues, organisms, and/or biologically active chemicalcompound(s), such as analogs or mimetics of the aforementioned species.In some instances, the biological sample may include whole blood,lymphatic fluid, serum, plasma, sweat, tear, saliva, sputum,cerebrospinal fluid, amniotic fluid, seminal fluid, vaginal excretion,serous fluid, synovial fluid, pericardial fluid, peritoneal fluid,pleural fluid, transudates, exudates, cystic fluid, bile, urine, gastricfluid, intestinal fluid, fecal samples, liquids containing single ormultiple cells, liquids containing organelles, fluidized tissues,fluidized organisms, liquids containing multi-celled organisms,biological swabs and biological washes.

In some embodiments, the biological sample may include an addedmaterial, such as water, deionized water, saline solutions, acidicsolutions, basic solutions, detergent solutions and/or pH buffers. Theadded material may also include reagents that will be used during thedesignated assay protocol to conduct the biochemical reactions. Forexample, added liquids may include material to conduct multiplepolymerase-chain-reaction (PCR) cycles with the biological sample.

It should be understood, however, that the biological sample that isanalyzed may be in a different form or state than the biological sampleloaded into the system 100. For example, the biological sample loadedinto the system 100 may include whole blood or saliva that issubsequently treated (e.g. via separation or amplification procedures)to provide prepared nucleic acids. The prepared nucleic acids may thenbe analyzed (e.g., quantified by PCR or sequenced by SBS) by the system100. Accordingly, when the term “biological sample” is used whiledescribing a first operation, such as PCR, and used again whiledescribing a subsequent second operation, such as sequencing, it isunderstood that the biological sample in the second operation may bemodified with respect to the biological sample prior to or during thefirst operation. For example, a sequencing step (e.g. SBS) may becarried out on amplicon nucleic acids that were produced from templatenucleic acids that were amplified in a prior amplification step (e.g.PCR). In this case the amplicons are copies of the templates and theamplicons are present in higher quantity compared to the quantity of thetemplates.

In some embodiments, the system 100 may automatically prepare a samplefor biochemical analysis based on a substance provided by the user(e.g., whole blood or saliva). However, in other embodiments, the system100 may analyze biological samples that are partially or preliminarilyprepared for analysis by the user. For example, the user may provide asolution including nucleic acids that were already isolated and/oramplified from whole blood.

As used herein, a “designated reaction” includes a change in at leastone of a chemical, electrical, physical, or optical property (orquality) of an analyte-of-interest. In particular embodiments, thedesignated reaction is an associative binding event (e.g., incorporationof a fluorescently labeled biomolecule with the analyte-of-interest).The designated reaction can be a dissociative binding event (e.g.,release of a fluorescently labeled biomolecule from ananalyte-of-interest). The designated reaction may be a chemicaltransformation, chemical change, or chemical interaction. The designatedreaction may also be a change in electrical properties. For example, thedesignated reaction may be a change in ion concentration within asolution. Exemplary reactions include, but are not limited to, chemicalreactions such as reduction, oxidation, addition, elimination,rearrangement, esterification, amidation, etherification, cyclization,or substitution; binding interactions in which a first chemical binds toa second chemical; dissociation reactions in which two or more chemicalsdetach from each other; fluorescence; luminescence; bioluminescence;chemiluminescence; and biological reactions, such as nucleic acidreplication, nucleic acid amplification, nucleic acid hybridization,nucleic acid ligation, phosphorylation, enzymatic catalysis, receptorbinding, or ligand binding. The designated reaction can also be additionor elimination of a proton, for example, detectable as a change in pH ofa surrounding solution or environment. An additional designated reactioncan be detecting the flow of ions across a membrane (e.g., natural orsynthetic bilayer membrane), for example as ions flow through a membranethe current is disrupted and the disruption can be detected. Fieldsensing of charged tags can also be used as can thermal sensing andother analytical sensing techniques known in the art

In particular embodiments, the designated reaction includes theincorporation of a fluorescently-labeled molecule to an analyte. Theanalyte may be an oligonucleotide and the fluorescently-labeled moleculemay be a nucleotide. The designated reaction may be detected when anexcitation light is directed toward the oligonucleotide having thelabeled nucleotide, and the fluorophore emits a detectable fluorescentsignal. In alternative embodiments, the detected fluorescence is aresult of chemiluminescence or bioluminescence. A designated reactionmay also increase fluorescence (or Førster) resonance energy transfer(FRET), for example, by bringing a donor fluorophore in proximity to anacceptor fluorophore, decrease FRET by separating donor and acceptorfluorophores, increase fluorescence by separating a quencher from afluorophore or decrease fluorescence by co-locating a quencher andfluorophore.

As used herein, a “reaction component” includes any substance that maybe used to obtain a designated reaction. For example, reactioncomponents include reagents, catalysts such as enzymes, reactants forthe reaction, samples, products of the reaction other biomolecules,salts, metal cofactors, chelating agents and pH buffer solutions (e.g.,hydrogenation buffer). The reaction components may be delivered,individually in solutions or combined in one or more mixture, to variouslocations in a fluidic network. For instance, a reaction component maybe delivered to a reaction chamber where the biological sample isimmobilized. The reaction component may interact directly or indirectlywith the biological sample. In some embodiments, the removable cartridge104 is pre-loaded with one or more of the reaction components that arenecessary for carrying out a designated assay protocol. Preloading canoccur at one location (e.g. a manufacturing facility) prior to receiptof the cartridge 104 by a user (e.g. at a customer's facility).

In some embodiments, the base instrument 102 may be configured tointeract with one removable cartridge 104 per session. After thesession, the removable cartridge 104 may be replaced with anotherremovable cartridge 104. In other embodiments, the base instrument 102may be configured to interact with more than one removable cartridge 104per session. As used herein, the term “session” includes performing atleast one of sample preparation and/or biochemical analysis protocol.Sample preparation may include separating, isolating, modifying and/oramplifying one or more component of the biological sample so that theprepared biological sample is suitable for analysis. In someembodiments, a session may include continuous activity in which a numberof controlled reactions are conducted until (a) a designated number ofreactions have been conducted, (b) a designated number of events havebeen detected, (c) a designated period of system time has elapsed, (d)signal-to-noise has dropped to a designated threshold; (e) a targetcomponent has been identified; (f) system failure or malfunction hasbeen detected and/or (g) one or more of the resources for conducting thereactions has depleted. Alternatively, a session may include pausingsystem activity for a period of time (e.g., minutes, hours, days, weeks)and later completing the session until at least one of (a)-(g) occurs.

An assay protocol may include a sequence of operations for conductingthe designated reactions, detecting the designated reactions, and/oranalyzing the designated reactions. Collectively, the removablecartridge 104 and the base instrument 102 may include the componentsthat are necessary for executing the different operations. Theoperations of an assay protocol may include fluidic operations,thermal-control operations, detection operations, and/or mechanicaloperations. A fluidic operation includes controlling the flow of fluid(e.g., liquid or gas) through the system 100, which may be actuated bythe base instrument 102 and/or by the removable cartridge 104. Forexample, a fluidic operation may include controlling a pump to induceflow of the biological sample or a reaction component into a detectionzone. A thermal-control operation may include controlling a temperatureof a designated portion of the system 100. By way of example, athermal-control operation may include raising or lowering a temperatureof a polymerase chain reaction (PCR) zone where a liquid that includesthe biological sample is stored. A detection operation may includecontrolling activation of a detector or monitoring activity of thedetector to detect predetermined properties, qualities, orcharacteristics of the biological sample. As one example, the detectionoperation may include capturing images of a designated area thatincludes the biological sample to detect fluorescent emissions from thedesignated area. The detection operation may include controlling a lightsource to illuminate the biological sample or controlling a detector toobserve the biological sample. A mechanical operation may includecontrolling a movement or position of a designated component. Forexample, a mechanical operation may include controlling a motor to movea valve-control component in the base instrument 102 that operablyengages a rotatable valve in the removable cartridge 104. In some cases,a combination of different operations may occur concurrently. Forexample, the detector may capture images of the detection zone as thepump controls the flow of fluid through the detection zone. In somecases, different operations directed toward different biological samplesmay occur concurrently. For instance, a first biological sample may beundergoing amplification (e.g., PCR) while a second biological samplemay be undergoing detection.

A “liquid,” as used herein, is a substance that is relativelyincompressible and has a capacity to flow and to conform to a shape of acontainer or a channel that holds the substance. A liquid may be aqueousbased and include polar molecules exhibiting surface tension that holdsthe liquid together. A liquid may also include non-polar molecules, suchas in an oil-based or non-aqueous substance. It is understood thatreferences to a liquid in the present application may include a liquidthat was formed from the combination of two or more liquids. Forexample, separate reagent solutions may be later combined to conductdesignated reactions.

The removable cartridge 104 is configured to separably engage orremovably couple to the base instrument 102. As used herein, when theterms “separably engaged” or “removably coupled” (or the like) are usedto describe a relationship between a removable cartridge and a baseinstrument, the term is intended to mean that a connection between theremovable cartridge and the base instrument is readily separable withoutdestroying the base instrument. Accordingly, the removable cartridge maybe separably engaged to the base instrument in an electrical manner suchthat the electrical contacts of the base instrument are not destroyed.The removable cartridge may be separably engaged to the base instrumentin a mechanical manner such that features of the base instrument thathold the removable cartridge are not destroyed. The removable cartridgemay be separably engaged to the base instrument in a fluidic manner suchthat the ports of the base instrument are not destroyed. The baseinstrument is not considered to be “destroyed,” for example, if only asimple adjustment to the component (e.g., realigning) or a simplereplacement (e.g., replacing a nozzle) is required. Components (e.g.,the removable cartridge 104 and the base instrument 102) may be readilyseparable when the components can be separated from each other withoutundue effort or a significant amount of time spent in separating thecomponents. In some embodiments, the removable cartridge 104 and thebase instrument 102 may be readily separable without destroying eitherthe removable cartridge 104 or the base instrument 102.

In some embodiments, the removable cartridge 104 may be permanentlymodified or partially damaged during a session with the base instrument102. For instance, containers holding liquids may include foil coversthat are pierced to permit the liquid to flow through the system 100. Insuch embodiments, the foil covers may be damaged such that it may benecessary to replace the damaged container with another container. Inparticular embodiments, the removable cartridge 104 is a disposablecartridge such that the removable cartridge 104 may be replaced andoptionally disposed after a single use.

In other embodiments, the removable cartridge 104 may be used for morethan one session while engaged with the base instrument 102 and/or maybe removed from the base instrument 102, reloaded with reagents, andre-engaged to the base instrument 102 to conduct additional designatedreactions. Accordingly, the removable cartridge 104 may be refurbishedin some cases such that the same removable cartridge 104 may be usedwith different consumables (e.g., reaction components and biologicalsamples). Refurbishing can be carried out at a manufacturing facilityafter the cartridge has been removed from a base instrument located at acustomer's facility.

As shown in FIG. 1A, the removable cartridge 104 includes a fluidicnetwork 106 that may hold and direct fluids (e.g., liquids or gases)therethrough. The fluidic network 106 includes a plurality ofinterconnected fluidic elements that are capable of storing a fluidand/or permitting a fluid to flow therethrough. Non-limiting examples offluidic elements include channels, ports of the channels, cavities,storage modules, reservoirs of the storage modules, reaction chambers,waste reservoirs, detection chambers, multipurpose chambers for reactionand detection, and the like. The fluidic elements may be fluidicallycoupled to one another in a designated manner so that the system 100 iscapable of performing sample preparation and/or analysis.

As used herein, the term “fluidically coupled” (or like term) refers totwo spatial regions being connected together such that a liquid or gasmay be directed between the two spatial regions. In some cases, thefluidic coupling permits a fluid to be directed back and forth betweenthe two spatial regions. In other cases, the fluidic coupling isuni-directional such that there is only one direction of flow betweenthe two spatial regions. For example, an assay reservoir may befluidically coupled with a channel such that a liquid may be transportedinto the channel from the assay reservoir. However, in some embodiments,it may not be possible to direct the fluid in the channel back to theassay reservoir. In particular embodiments, the fluidic network 106 isconfigured to receive a biological sample and direct the biologicalsample through sample preparation and/or sample analysis. The fluidicnetwork 106 may direct the biological sample and other reactioncomponents to a waste reservoir.

One or more embodiments may include retaining the biological sample(e.g., template nucleic acid) at a designated location where thebiological sample is analyzed. As used herein, the term “retained,” whenused with respect to a biological sample, includes substantiallyattaching the biological sample to a surface or confining the biologicalsample within a designated space. As used herein, the term“immobilized,” when used with respect to a biological sample, includessubstantially attaching the biological sample to a surface in or on asolid support. Immobilization may include attaching the biologicalsample at a molecular level to the surface. For example, a biologicalsample may be immobilized to a surface of a substrate using adsorptiontechniques including non-covalent interactions (e.g., electrostaticforces, van der Waals, and dehydration of hydrophobic interfaces) andcovalent binding techniques where functional groups or linkersfacilitate attaching the biological sample to the surface. Immobilizinga biological sample to a surface of a substrate may be based upon theproperties of the surface of the substrate, the liquid medium carryingthe biological sample, and the properties of the biological sampleitself. In some cases, a substrate surface may be functionalized (e.g.,chemically or physically modified) to facilitate immobilizing thebiological sample to the substrate surface. The substrate surface may befirst modified to have functional groups bound to the surface. Thefunctional groups may then bind to the biological sample to immobilizethe biological sample thereon. In some cases, a biological sample can beimmobilized to a surface via a gel, for example, as described in USPatent Publ. Nos. 2011/0059865 A1 and 2014/0079923 A1, each of which isincorporated herein by reference in its entirety.

In some embodiments, nucleic acids can be immobilized to a surface andamplified using bridge amplification. Useful bridge amplificationmethods are described, for example, in U.S. Pat. No. 5,641,658; WO07/010251, U.S. Pat. No. 6,090,592; U.S. Patent Publ. No. 2002/0055100A1; U.S. Pat. No. 7,115,400; U.S. Patent Publ. No. 2004/0096853 A1; U.S.Patent Publ. No. 2004/0002090 A1; U.S. Patent Publ. No. 2007/0128624 A1;and U.S. Patent Publ. No. 2008/0009420 A1, each of which is incorporatedherein in its entirety. Another useful method for amplifying nucleicacids on a surface is rolling circle amplification (RCA), for example,using methods set forth in further detail below. In some embodiments,the nucleic acids can be attached to a surface and amplified using oneor more primer pairs. For example, one of the primers can be in solutionand the other primer can be immobilized on the surface (e.g.,5′-attached). By way of example, a nucleic acid molecule can hybridizeto one of the primers on the surface followed by extension of theimmobilized primer to produce a first copy of the nucleic acid. Theprimer in solution then hybridizes to the first copy of the nucleic acidwhich can be extended using the first copy of the nucleic acid as atemplate. Optionally, after the first copy of the nucleic acid isproduced, the original nucleic acid molecule can hybridize to a secondimmobilized primer on the surface and can be extended at the same timeor after the primer in solution is extended. In any embodiment, repeatedrounds of extension (e.g., amplification) using the immobilized primerand primer in solution provide multiple copies of the nucleic acid. Insome embodiments, the biological sample may be confined within apredetermined space with reaction components that are configured to beused during amplification of the biological sample (e.g., PCR).

In the illustrated embodiment, the removable cartridge 104 includes acartridge housing 110 having a plurality of housing sides 111-114. Thehousing sides 111-114 include non-mating sides 111-113 and a mating side114. The mating side 114 is configured to engage the base instrument102. In the illustrated embodiment, the cartridge housing 110 forms asubstantially unitary structure. In alternative embodiments, thecartridge housing 110 may be constructed by one or more sub-componentsthat are combined by a user of the system 100. The sub-components may becombined before the removable cartridge 104 is separably engaged to thebase instrument 102 or after one of the sub-components is separablyengaged to the base instrument 102. For example, a storage module 150may be held by a first sub-housing (not shown) and a remainder of theremovable cartridge 104 (e.g., fluidic network and imaging device) mayinclude a second sub-housing (not shown). The first and secondsub-housings may be combined to form the cartridge housing 110.

The fluidic network 106 is held by the cartridge housing 110 andincludes a plurality of sample ports 116 that open to the non-matingside 112. In alternative embodiments, the sample ports 116 may belocated along the non-mating sides 111 or 113 or may be located alongthe mating side 114. Each of the sample ports 116 is configured toreceive a biological sample. By way of example only, the biologicalsample may be whole blood or saliva. In some embodiments, the biologicalsample may be nucleic acids and other materials (e.g., reagents,buffers, etc.) for conducting PCR. Although three sample ports 116 areshown in FIG. 1A, embodiments may include only one sample port, twosample ports, or more than three sample ports.

The fluidic network 106 also includes a fluidic-coupling port 118 thatopens to the mating side 114 and is exposed to an exterior of thecartridge housing 110. The fluidic-coupling port 118 is configured tofluidically couple to a system pump 119 of the base instrument 102. Thefluidic-coupling port 118 is in flow communication with a pump channel133 that is part of the fluidic network 106. During operation of thesystem 100, the system pump 119 is configured to provide a negativepressure for inducing a flow of fluid through the pump channel 133 andthrough a remainder of the fluidic network 106. For example, the systempump 119 may induce flow of the biological sample from the sample port116 to a sample-preparation region 132, wherein the biological samplemay be prepared for subsequent analysis. The system pump 119 may induceflow of the biological sample from the sample-preparation region 132 toa reaction chamber 126, wherein detection operations are conducted toobtain data (e.g., imaging data) of the biological sample. The systempump 119 may also induce flow of fluid from reservoirs 151, 152 of astorage module 150 to the reaction chamber 126. After the detectionoperations are conducted, the system pump 119 may induce flow of thefluid into a waste reservoir 128.

In addition to the fluidic network 106, the removable cartridge 104 mayinclude one or more mechanical interfaces 117 that may be controlled bythe base instrument 102. For example, the removable cartridge 104 mayinclude a valve assembly 120 having a plurality of flow-control valves121-123 that are operably coupled to the fluidic network 106. Each ofthe flow-control valves 121-123 may represent a mechanical interface 117that is controlled by the base instrument 102. For instance, theflow-control valves 121-123 may be selectively activated or controlledby the base instrument 102, in conjunction with selective activation ofthe system pump 119, to control a flow of fluid within the fluidicnetwork 106.

For example, in the illustrated embodiment, the fluidic network 106includes a sample channel 131 that is immediately downstream from and inflow communication with the sample ports 116. Only a single samplechannel 131 is shown in FIG. 1A, but alternative embodiments may includemultiple sample channels 131. The sample channel 131 may include thesample-preparation region 132. The valve assembly 120 includes a pair ofchannel valves 121, 122. The channel valves 121, 122 may be selectivelyactivated by the base instrument 102 to impede or block flow of thefluid through the sample channel 131. In particular embodiments, thechannel valves 121, 122 may be activated to form a seal that retains adesignated volume of liquid within the sample-preparation region 132 ofthe sample channel 131. The designated volume within thesample-preparation region 132 may include the biological sample.

The valve assembly 120 may also include a movable valve 123. The movablevalve 123 may be similar to the rotatable valve assembly 1410 (shown inFIGS. 27A, 27B). The movable valve 123 has a valve body 138 that mayinclude at least one flow channel 140 that extends between correspondingports. The valve body 138 is capable of moving between differentpositions to align the ports with corresponding ports of the fluidicnetwork 106. For example, a position of the movable valve 123 maydetermine the type of fluid that flows into the reaction chamber 126. Ina first position, the movable valve 123 may align with a correspondingport of the sample channel 131 to provide the biological sample to thereaction chamber 126. In a second position, the movable valve 123 mayalign with one or more corresponding ports of reservoir channels 161,162 that are in flow communication with the reservoirs 151, 152,respectively, of the storage module 150. Each reservoir 151, 152 isconfigured to store a reaction component that may be used to conduct thedesignated reactions. The reservoir channels 161, 162 are locateddownstream from and in flow communication with the reservoirs 151, 152,respectively. In some embodiments, the movable valve 123 may move,separately, to different positions to align with the corresponding portsof the reservoir channels.

In the illustrated embodiment, the movable valve 123 is a rotatablevalve that is configured to rotate about an axis 142. Accordingly, themovable valve 123 is hereinafter referred to as the rotatable valve 123.However, it should be understood that alternative embodiments mayinclude movable valves that do not rotate to different positions. Insuch embodiments, the movable valve may slide in one or more lineardirections to align the corresponding ports. Rotatable valves andlinear-movement valves set forth herein may be similar to theapparatuses described in International Application No.PCT/US2013/032309, filed on Mar. 15, 2013, which is incorporated hereinby reference in its entirety.

In some embodiments, the biological sample is illuminated by a lightsource 158 of the base instrument 102. Alternatively, the light source158 may be incorporated with the removable cartridge 104. For example,the biological sample may include one or more fluorophores that providelight emissions when excited by a light having a suitable wavelength. Inthe illustrated embodiment, the removable cartridge 104 has an opticalpath 154. The optical path 154 is configured to permit illuminationlight 156 from the light source 158 of the base instrument 102 to beincident on the biological sample within the reaction chamber 126. Thus,the reaction chamber may have one or more optically transparent sides orwindows. The optical path 154 may include one or more optical elements,such as lenses, reflectors, fiber-optic lines, and the like, thatactively direct the illumination light 156 to the reaction chamber 126.In an exemplary embodiment, the light source 158 may be a light-emittingdiode (LED). However, in alternative embodiments, the light source 158may include other types of light-generating devices such as lasers orlamps.

In some embodiments, the detection assembly 108 includes an imagingdetector 109 and the reaction chamber 126. The imaging detector 109 isconfigured to detect designated reactions within the reaction chamber126. The imaging detector 109 may be similar to the CMOS image sensor262 (shown in FIG. 40 ). In some embodiments, the imaging detector 109may be positioned relative to the reaction chamber 126 to detect lightsignals (e.g., absorbance, reflection/refraction, or light emissions)from the reaction chamber 126. The imaging detector 109 may include oneor more imaging devices, such as a charge-coupled device (CCD) camera orcomplementary-metal-oxide semiconductor (CMOS) imager. In someembodiments, the imaging detector 109 may detect light signals that areemitted from chemilluminescence. Yet still in other embodiments, thedetection assembly 108 may not be limited to imaging applications. Forexample, the detection assembly 108 may be one or more electrodes thatdetect an electrical property of a liquid.

As set forth herein, the base instrument 102 is configured to operablyengage the removable cartridge 104 and control various operations withinthe removable cartridge 104 to conduct the designated reactions and/orobtain data of the biological sample. To this end, the mating side 114is configured to permit or allow the base instrument 102 to controloperation of one or more components of the removable cartridge 104. Forexample, the mating side 114 may include a plurality of access openings171-173 that permit the valves 121-123 to be controlled by the baseinstrument 102. The mating side 114 may also include an access opening174 that is configured to receive a thermal block 206 of the baseinstrument 102. The access opening 174 extends along the sample channel131. As shown, the access openings 171-174 open to the mating side 114.

The base instrument 102 has a control side 202 configured to separablyengage the mating side 114 of the removable cartridge 104. The matingside 114 of the removable cartridge 104 and the control side 202 of thebase instrument 102 may collectively define a system interface 204. Thesystem interface 204 represents a common boundary between the removablecartridge 104 and the base instrument 102 through which the baseinstrument 102 and the removable cartridge 104 are operably engaged.More specifically, the base instrument 102 and the removable cartridge104 are operably engaged along the system interface 204 such that thebase instrument 102 may control various features of the removablecartridge 104 through the mating side 114. For instance, the baseinstrument 102 may have one or more controllable components that controlcorresponding components of the removable cartridge 104.

In some embodiments, the base instrument 102 and the removable cartridge104 are operably engaged such that the base instrument 102 and theremovable cartridge 104 are secured to each other at the systeminterface 204 with at least one of an electric coupling, thermalcoupling, optical coupling, valve coupling, or fluidic couplingestablished through the system interface 204. In the illustratedembodiment, the base instrument 102 and the removable cartridge 104 areconfigured to have an electric coupling, a thermal coupling, a valvecoupling, and an optical coupling. More specifically, the baseinstrument 102 and the removable cartridge 104 may communicate dataand/or electrical power through the electric coupling. The baseinstrument 102 and the removable cartridge 104 may convey thermal energyto and/or from each other through the thermal coupling, and the baseinstrument 102 and the removable cartridge 104 may communicate lightsignals (e.g., the illumination light) through the optical coupling.

In the illustrated embodiment, the system interface 204 is asingle-sided interface 204. For example, the control side 202 and thehousing side 114 are generally planar and face in opposite directions.The system interface 204 is single-sided such that that the removablecartridge 104 and the base instrument 102 are operably coupled to eachother only through the mating side 114 and the control side 202. Inalternative embodiments, the system interface may be a multi-sidedinterface. For example, at least 2, 3, 4, or 5 sides of a removablecartridge may be mating sides that are configured to couple with a baseinstrument. The multiple sides may be planar and may be arrangedorthogonally or opposite each other (e.g. surrounding all or part of arectangular volume).

To control operations of the removable cartridge 104, the baseinstrument 102 may include valve actuators 211-213 that are configuredto operably engage the flow-control valves 121-123, a thermal block 206that is configured to provide and/or remove thermal energy from thesample-preparation region 132, and a contact array 208 of electricalcontacts 209. The base instrument 102 may also include the light source158 positioned along the control side 202. The base instrument 102 mayalso include the system pump 119 having a control port 210 positionedalong the control side 202.

The system 100 may also include a locking mechanism 176. In theillustrated embodiment, the locking mechanism 176 includes a rotatablelatch 177 that is configured to engage a latch-engaging element 178 ofthe removable cartridge 104. Alternatively, the removable cartridge 104may include the rotatable latch 177 and the base instrument 102 mayinclude the latch-engaging element 178. When the removable cartridge 104is mounted to the base instrument 102, the latch 177 may be rotated andengage the latching-engaging element 176. A camming effect generated bythe locking mechanism 176 may urge or drive the removable cartridge 104toward the base instrument 102 to secure the removable cartridge 104thereto.

The base instrument 102 may include a user interface 125 that isconfigured to receive user inputs for conducting a designated assayprotocol and/or configured to communicate information to the userregarding the assay. The user interface 125 may be incorporated with thebase instrument 102. For example, the user interface 125 may include atouchscreen that is attached to a housing of the base instrument 102 andconfigured to identify a touch from the user and a location of the touchrelative to information displayed on the touchscreen. Alternatively, theuser interface 125 may be located remotely with respect to the baseinstrument 102.

The base instrument 102 may also include a system controller 220 that isconfigured to control operation of at least one of the valve actuators211-213, the thermal block 206, the contact array 208, the light source158, or the system pump 119. The system controller 220 is illustratedconceptually as a collection of circuitry modules, but may beimplemented utilizing any combination of dedicated hardware boards,DSPs, processors, etc. Alternatively, the system controller 220 may beimplemented utilizing an off-the-shelf PC with a single processor ormultiple processors, with the functional operations distributed betweenthe processors. As a further option, the circuitry modules describedbelow may be implemented utilizing a hybrid configuration in whichcertain modular functions are performed utilizing dedicated hardware,while the remaining modular functions are performed utilizing anoff-the-shelf PC and the like.

The system controller 220 may include a plurality of circuitry modules221-224 that are configured to control operation of certain componentsof the base instrument 102 and/or the removable cartridge 104. Forinstance, the circuitry module 221 may be a flow-control module 221 thatis configured to control flow of fluids through the fluidic network 106.The flow-control module 221 may be operably coupled to the valveactuators 211-213 and the system pump 119. The flow-control module 221may selectively activate the valve actuators 211-213 and the system pump119 to induce flow of fluid through one or more paths and/or to blockflow of fluid through one or more paths.

By way of example only, the valve actuator 213 may rotatably engage therotatable valve 123. The valve actuator 213 may include a rotating motor214 that is configured to drive (e.g., rotate) the valve actuator 213.The flow-control module 221 may activate the valve actuator 213 to movethe rotatable valve 123 to a first rotational position. With therotatable valve 123 in the first rotational position, the flow-controlmodule 221 may activate the system pump 219 thereby drawing thebiological sample from the sample-preparation region 132 and into thereaction chamber 126. The flow-control module 221 may then activate thevalve actuator 213 to move the rotatable valve 123 to a secondrotational position. With the rotatable valve 123 in the secondrotational position, the flow-control module 221 may activate the systempump 219 thereby drawing one or more of the reaction components from thecorresponding reservoir(s) and into the reaction chamber 126. In someembodiments, the system pump 219 may be configured to provide positivepressure such that the fluid is actively pumped in an oppositedirection. Such operations may be used to add multiple liquids into acommon reservoir thereby mixing the liquids within the reservoir.Accordingly, the fluidic-coupling port 118 may permit fluid (e.g., gas)to exit the cartridge housing 110 or may receive fluid into thecartridge housing 110.

The system controller 220 may also include a thermal-control module 222.The thermal-control module 222 may control the thermal block 206 toprovide and/or remove thermal energy from the sample-preparation region132. In one particular example, the thermal block 206 may increaseand/or decrease a temperature that is experienced by the biologicalsample within the sample channel 131 in accordance with a PCR protocol.Although not shown, the system 100 may include additional thermaldevices that are positioned adjacent to the sample-preparation region132. For example, the removable cartridge 104 may include a thermaldevice that is similar to the flexible PCB heater 1412 (shown in FIGS.27A, 27B).

The system controller 220 may also include a detection module 223 thatis configured to control the detection assembly 108 to obtain dataregarding the biological sample. The detection module 223 may controloperation of the detection assembly 108 through the contact array 208.For example, the detection assembly 108 may be communicatively engagedto a contact array 194 of electrical contacts 196 along the mating side114. In some embodiment, the electrical contacts 196 may be flexiblecontacts (e.g., pogo contacts or contact beams) that are capable ofrepositioning to and from the mating side 114. The electrical contacts196 are exposed to an exterior of the cartridge housing and areelectrically coupled to the detection assembly 108. The electricalcontacts 196 may be referenced as input/output (I/O) contacts. When thebase instrument 102 and the removable cartridge 104 are operablyengaged, the detection module 223 may control the detection assembly 108to obtain data at predetermined times or for predetermined time periods.By way of example, the detection module 223 may control the detectionassembly 108 to capture an image of the reaction chamber 126 when thebiological sample has a fluorophore attached thereto. A number of imagesmay be obtained.

Optionally, the system controller 220 includes an analysis module 224that is configured to analyze the data to provide at least partialresults to a user of the system 100. For example, the analysis module224 may analyze the imaging data provided by the imaging detector 109.The analysis may include identifying a sequence of nucleic acids of thebiological sample.

The system controller 220 and/or the circuitry modules 221-224 mayinclude one or more logic-based devices, including one or moremicrocontrollers, processors, reduced instruction set computers (RISC),application specific integrated circuits (ASICs), field programmablegate array (FPGAs), logic circuits, and any other circuitry capable ofexecuting functions described herein. In an exemplary embodiment, thesystem controller 220 and/or the circuitry modules 221-224 execute a setof instructions that are stored therein in order to perform one or moreassay protocols. Storage elements may be in the form of informationsources or physical memory elements within the base instrument 102and/or the removable cartridge 104. The protocols performed by the assaysystem 100 may be to carry out, for example, quantitative analysis ofDNA or RNA, protein analysis, DNA sequencing (e.g.,sequencing-by-synthesis (SBS)), sample preparation, and/or preparationof fragment libraries for sequencing.

The set of instructions may include various commands that instruct thesystem 100 to perform specific operations such as the methods andprocesses of the various embodiments described herein. The set ofinstructions may be in the form of a software program. As used herein,the terms “software” and “firmware” are interchangeable, and include anycomputer program stored in memory for execution by a computer, includingRAM memory, ROM memory, EPROM memory, EEPROM memory, and non-volatileRAM (NVRAM) memory. The above memory types are exemplary only, and arethus not limiting as to the types of memory usable for storage of acomputer program.

The software may be in various forms such as system software orapplication software. Further, the software may be in the form of acollection of separate programs, or a program module within a largerprogram or a portion of a program module. The software also may includemodular programming in the form of object-oriented programming. Afterobtaining the detection data, the detection data may be automaticallyprocessed by the system 100, processed in response to user inputs, orprocessed in response to a request made by another processing machine(e.g., a remote request through a communication link).

The system controller 220 may be connected to the other components orsub-systems of the system 100 via communication links, which may behardwired or wireless. The system controller 220 may also becommunicatively connected to off-site systems or servers. The systemcontroller 220 may receive user inputs or commands, from a userinterface (not shown). The user interface may include a keyboard, mouse,a touch-screen panel, and/or a voice recognition system, and the like.

The system controller 220 may serve to provide processing capabilities,such as storing, interpreting, and/or executing software instructions,as well as controlling the overall operation of the system 100. Thesystem controller 220 may be configured and programmed to control dataand/or power aspects of the various components. Although the systemcontroller 220 is represented as a single structure in FIG. 1A, it isunderstood that the system controller 220 may include multiple separatecomponents (e.g., processors) that are distributed throughout the system100 at different locations. In some embodiments, one or more componentsmay be integrated with a base instrument and one or more components maybe located remotely with respect to the base instrument.

FIG. 1B is a flow chart illustrating a method 180 of conductingdesignated reactions for at least one of sample preparation or sampleanalysis. In particular embodiments, the method 180 may includesequencing nucleic acids. The method 180 may employ structures oraspects of various embodiments (e.g., systems and/or methods) discussedherein. In various embodiments, certain steps may be omitted or added,certain steps may be combined, certain steps may be performedsimultaneously, certain steps may be performed concurrently, certainsteps may be split into multiple steps, certain steps may be performedin a different order, or certain steps or series of steps may bere-performed in an iterative fashion.

For example, the method 180 may include providing, at 182, a removablecartridge having a cartridge housing. The removable cartridge mayinclude a fluidic network disposed within the cartridge housing. Theremovable cartridge may also include a flow-control valve that isoperably coupled to the fluidic network and movable relative to thefluidic network. The flow-control valve may be, for example, a channelvalve or a movable valve, such as a rotatable valve. The cartridgehousing may include a housing side that defines an exterior of theremovable cartridge.

The method 180 may also include mounting (e.g., contacting), at 184, theremovable cartridge to a base instrument. The housing side of theremovable cartridge may separably engage a control side of the baseinstrument to collectively define a system interface. The baseinstrument includes a valve actuator that engages the flow-control valvethrough the system interface. For example, the valve actuator mayinclude an elongated body that clears the control side and is insertedinto an access opening along the housing side of the removablecartridge. Optionally, the valve actuator directly engages a portion ofthe flow-control valve.

At 186, one or more biological samples may be received by the removablecartridge. For example, a user may use a pipettor to add the biologicalsample(s) to sample ports that are in flow communication with thefluidic network. The receiving at 186 may occur before or after thecontacting at 184. The method 180 may include fluidically directing, at188, a biological sample to flow through the fluidic network of theremovable cartridge to conduct at least one of sample analysis or samplepreparation in the cartridge. For example, the biological sample may bedirected to a sample-preparation region of the fluidic network, whereinthe flow of the biological sample is controlled by action of the valveactuator on the flow-control valve. The biological sample may undergo anamplification process, such as PCR, while the biological sample issealed within the sample-preparation region. As another example, thebiological sample may be directed to flow into a reaction chamber,wherein the flow of the biological sample is controlled by action of thevalve actuator on the flow-control valve.

Optionally, at 190, the method 180 includes detecting the biologicalsample using an imaging detector directed to the reaction chamber. Thedetection assembly may be held by at least one of the removablecartridge or the base instrument. For example, the detection assemblymay be incorporated within the removable cartridge. The base instrumentmay electrically couple to the detection assembly to control operationof the detection assembly. Optionally, fluidically directing thebiological sample at 186 and/or imaging the biological sample at 190 maybe repeated multiple times in accordance with a predetermined scheduleor sequence.

In some embodiments, the method 180 includes removing, at 192, theremovable cartridge from the base instrument. After the assay protocolhas been completed, the removable cartridge may be removed from the baseinstrument. In some cases, the removable cartridge may be re-filled orrefurbished. For example, the removable cartridge may be decontaminatedand/or sterilized and the used storage module may be replaced by a newstorage module. The method 180 may then return to 182 in which anotherremovable cartridge is provided and mounted, at 184, with respect to thesame base instrument. In a similar manner as the first removablecartridge, the housing side of the second removable cartridge mayseparably engage the control side of the base instrument to collectivelydefine the system interface.

FIG. 2 is a schematic diagram of a system 300 that is configured toconduct at least one of biochemical analysis or sample preparation. Thesystem 300 may include identical or similar features as the system 100(FIG. 1A). For example, the system 300 includes a base instrument 302and a removable cartridge 304 that is configured to separably engage thebase instrument 302. The base instrument 302 and the removable cartridge304 may have similar features as the base instrument 102 and theremovable cartridge 104, respectively, (shown in FIG. 1A). As shown inFIG. 2 , the base instrument 302 has an instrument housing 303 thatincludes an instrument side 306 and a cartridge-receiving slot 308 thatopens to the instrument side 306. In some embodiments, the instrumentside 306 may represent a top, with respect to gravity, of the baseinstrument 302 and partially form an exterior of the instrument housing303. In the illustrated embodiment, the cartridge-receiving slot 308 isdefined by interior docking or control sides 311-313 of the instrumenthousing 303. The control sides 311 and 313 oppose each other and thecontrol side 312 extends between the control sides 311, 313. The controlside 312 may face an opening 316 to the cartridge-receiving slot 308.

The removable cartridge 304 is sized and shaped to be disposed withinthe cartridge-receiving slot 308 and operably engage the base instrument302. As shown, the removable cartridge 304 includes a cartridge housing320 that has housing sides 321-324. The housing sides 321-323 areconfigured to operably engage the docking or control sides 311-313 suchthat the base instrument 302 and the removable cartridge 304 establishat least one of an electric coupling, thermal coupling, opticalcoupling, and/or fluidic coupling. As such, the housing sides 321-323are hereinafter referred to as the mating sides 321-323. The housingside 324 does not operably engage the base instrument 302. Accordingly,the housing side 324 may be referred to as the non-mating side 324.

Similar to the removable cartridge 104 (FIG. 1A), the removablecartridge 304 includes a plurality of features and components forcontrolling operations within the removable cartridge 304 to conductdesignated reactions. For example, the removable cartridge 304 hassample ports 330 that open to the non-mating side 324 and are configuredto receive one or more biological samples. Alternatively, the sampleports 330 may open to one of the mating sides 321-323. In suchembodiments, the biological sample(s) may be deposited within the sampleports 330 prior to the removable cartridge 304 being loaded into thecartridge-receiving slot 308.

The removable cartridge 304 may also include a fluidic network 332having a sample-preparation region 334. The fluidic network 332 mayinclude or fluidically interconnect a number of other components of theremovable cartridge 304, such as a storage module 336, a movable valve338, a detection assembly 340 having an imaging detector 342, and awaste reservoir 344. Optionally, the removable cartridge 304 may alsoinclude an optical path 346 and a contact array 348. The components ofthe removable cartridge 304 may be similar to components described abovewith reference to the removable cartridge 304.

The base instrument 302 may have corresponding components that operablyengage the removable cartridge 304 to conduct the designated reactions.For example, the base instrument 302 includes a thermal block 350, avalve actuator 352, a light source 356, a contact array 358, and asystem pump 360. As the removable cartridge 304 is loaded into thecartridge-receiving slot 308 or after the removable cartridge 304 isloaded into the cartridge-receiving slot 308, the various components ofthe removable cartridge 304 and the base instrument 302 may engage oneanother. More specifically, when the removable cartridge 304 is operablyloaded into the base instrument 302, the thermal block 350 may belocated proximate to the sample-preparation region 334, the valveactuator 352 may operably engage the movable valve 338, the light source356 may communicatively couple to the optical path 346, the contactarray 358 may electrically engage the contact array 348, and the systempump 360 may communicatively engage the fluidic network 332.Accordingly, the removable cartridge 304 may be controlled by the baseinstrument 302 in a similar manner as the removable cartridge 104 iscontrolled by the base instrument 102.

The base instrument 302 may be configured to permit the removablecartridge 304 to be inserted freely into the cartridge-receiving slot308 without damaging components located on the control sides 311-313 orthe mating sides 321-323. For example, one or more of the components ofthe base instrument 302 are biased toward or moved toward the removablecartridge 304. In some embodiments, the thermal block 350 and the valveactuator 352 are secured to a component support 362. The componentsupport 362 may be biased toward the mating side 321 or moved toward themating side 321 after the removable cartridge 304 is disposed within thecartridge-receiving slot 308. In a similar manner, the system pump 360may be secured to a component support 364. The component support 364 maybe biased toward the mating side 323 or moved toward the mating side 323after the removable cartridge 304 is disposed within thecartridge-receiving slot 308.

The component supports 362, 364 may be automatically activated by asystem controller 370. For example, the system controller 370 maydetermine that the removable cartridge 304 is being loaded or hasalready been loaded into the cartridge-receiving slot 308. The systemcontroller 370 may then activate a driving mechanism or multiplemechanisms to drive the component supports 362, 364 toward the matingsides 321, 323. Alternatively, the component supports 362, 364 may beoperably linked to an operator-controlled mechanism or mechanisms that,once activated by a user of the system 300, may drive the componentsupports 362, 364 toward the mating sides 321, 323, respectively.Accordingly, the base instrument 302 may be configured to permit theremovable cartridge 304 to be advanced freely (e.g., without substantialsnagging or stubbing) into the cartridge-receiving slot 308.

Embodiments set forth herein include systems in which the removablecartridge and the base instrument may form a system interface that ismulti-sided. For example, each of the mating sides 321-323 operablyengages a corresponding control side that defines thecartridge-receiving slot 308. Collectively, the mating sides 321-323 andthe corresponding control sides 311-313 define a system interface, whichmay be referred to as a multi-sided interface. Such embodiments may bedesirable to balance forces experienced by the removable cartridge 304.For example, the thermal block 350 and the valve actuator 352 may applya force 374 in a first direction (as indicated by the arrow). The systempump 360 may apply a force 376 in an opposite second direction (asindicated by the arrow). An interaction between the contact arrays 348,358 may also provide a portion of the force 376.

In some embodiments, at least one of the forces 374, 376 facilitatesproviding intimate contact between the corresponding components. Forinstance, the force 374 may provide intimate contact between the thermalblock 350 and the sample-preparation region 334 to enable thermalcontrol of the sample-preparation region 334. Likewise, the force 374may permit the valve actuator 352 and the movable valve 338 to suitablyengage each other so that the valve actuator 352 may selectively controlthe movable valve 338. The force 376 may enable an intimate contactbetween corresponding electrical contacts of the contact arrays 348,358.

FIGS. 3 and 4 illustrate different systems having corresponding baseinstruments and removable cartridges and, in particular, illustratedifferent multi-sided interfaces that may be utilized by one or moreembodiments. For example, FIG. 3 is an end view of a system 400 thatincludes a base instrument 402 and a removable cartridge 404. The baseinstrument 402 includes an open-sided recess 406 that is sized andshaped to receive the removable cartridge 404. As shown, the open-sidedrecess 406 is formed by first and second control sides 411, 412 thatface in perpendicular directions with respect to each other. Morespecifically, the first and second control sides 411, 412 form anL-shaped recess. The first and second control sides 411, 412 operablyengage first and second mating sides 413, 414, respectively, of theremovable cartridge 404. Collectively, a multi-sided interface 415 isformed between the first control side 411 and the first mating side 413and the second control side 412 and the second mating side 414. Morespecifically, at least one of a valve coupling, fluidic coupling,electrical coupling, optical coupling, or thermal coupling may beestablished along each of the first and second mating sides 413, 414.

FIG. 4 is a top-down view of a system 420 that includes a baseinstrument 422 and a removable cartridge 424. The base instrument 422includes a cartridge-receiving slot 426, which may be similar oridentical to the cartridge-receiving slot 308 (FIG. 2 ). Thecartridge-receiving slot 426 is sized and shaped to receive theremovable cartridge 424. As shown, the cartridge-receiving slot 426 isformed by control sides 431-434. The control sides 431, 433 oppose eachother, and the control sides 432, 434 oppose each other. The controlsides 431-434 operably engage mating sides 441-444, respectively, of theremovable cartridge 424. Collectively, a multi-sided interface 427 isformed between the corresponding sides of the removable cartridge 424and the base instrument 422.

FIGS. 5-12 illustrate different valving mechanisms through which a baseinstrument may control (e.g., regulate) flow through a fluidic networkof a removable cartridge. Each of FIGS. 5-12 illustrates a cross-sectionof a system in which a valve coupling has been established between thebase instrument and the removable cartridge through a system interface.Each of FIGS. 5-12 illustrates a channel valve in which the baseinstrument may activate the channel valve to open and close acorresponding channel. For example, FIGS. 5 and 6 illustrates a portionof a system 500, which may be similar to the systems described above,such as the systems 100 (FIG. 1A), 300 (FIG. 2 ), 400 (FIG. 3 ), 420(FIG. 4 ).

FIGS. 5 and 6 illustrate a cross-section of a portion of a system 500having a base instrument 502 and a removable cartridge 504 that areoperably engaged along a system interface 506. As shown, the removablecartridge 504 has a cartridge housing 508 and a microfluidic body 510that is held by the cartridge housing 508. In the illustratedembodiment, the microfluidic body 510 includes a plurality of layers521-523 that are stacked side-by-side. The layers 521-523 may be printedcircuit board (PCB) layers, such as those described below with respectto FIGS. 14-75 . One or more of the layers 521-523 may be etched suchthat, when the layers 5212-523 are stacked side-by-side, themicrofluidic body 510 forms a sample channel 526. The sample channel 526is a portion of a fluidic network, such as the fluidic network 106 (FIG.1A), and includes a valve or interior cavity 528.

The removable cartridge 504 includes a channel valve 530 that isconfigured to regulate flow of a fluid through the sample channel 526.For example, the channel valve 530 may permit maximum clearance so thatthe fluid may flow unimpeded. The channel valve 530 may also impede theflow of fluid therethrough. As used herein, the term “impede” mayinclude slowing the flow of fluid or entirely blocking the flow offluid. As shown, the sample channel 530 includes first and second ports532, 534 that are in flow communication with the valve cavity 528. Fluidis configured to flow into the valve cavity 528 through the first port532 and out of the valve cavity 528 through the second port 534. In theillustrated embodiment, the channel valve 530 constitutes a flexiblemembrane that is capable of being flexed between first and secondconditions. The flexible membrane is in the first condition in FIG. 5and in the second condition in FIG. 6 . In particular embodiments, theflexible membrane is a flexible layer, such as the membrane layer 918(shown in FIGS. 23A, 23B). The flexible layer is configured to be pushedinto the valve cavity 528 to block the flow of fluid therethrough. Inalternative embodiments, the channel valve 530 may be another physicalelement that is capable of moving between different conditions orpositions to regulate flow of the fluid.

Also shown, the base instrument 502 includes a valve actuator 540 thatis configured to activate the channel valve 530. For instance, the valveactuator 540 may flex the flexible membrane between the first and secondconditions. The valve actuator 540 includes an elongated body 542, suchas a post or rod, that extends through the system interface 506. Morespecifically, the elongated body 542 clears a control side 544 of thebase instrument 502. The removable cartridge 504 has an access opening546 that receives the valve actuator 540. The access opening 546 opensto a mating side 548 of the removable cartridge 504. As shown, theelongated body 542 projects away from the control side 544 and into theaccess opening 546 of the mating side 548. The access opening 546permits the valve actuator 540 to directly engage the channel valve 530,which is a flexible membrane in the illustrated embodiment. In FIG. 5 ,the valve actuator 540 is in a first state or position. In FIG. 6 , thevalve actuator 540 is in a second state or position. In the secondposition, the valve actuator 540 has been moved a distance toward thechannel valve 530 and is engaged with the channel valve 530. The valveactuator 540 may deform the channel valve 530 such that the channelvalve 530 covers the first port 532. As such, a fluid flow through thefirst port 532 is blocked by the channel valve 530.

In some embodiments, the system 500 may have first and second channelvalves that are similar or identical to the channel valve 530 shown inFIGS. 5 and 6 , wherein the first channel valve is upstream with respectto a sample-preparation region (not shown) of the fluidic network andthe second channel valve is downstream with respect to thesample-preparation region. As such, the first and second channel valvesmay effectively seal a fluid, which may contain the biological sample,within the sample-preparation region. The fluid having the biologicalsample may then be heated to subject the fluid to an amplificationprotocol, such as a PCR protocol.

FIGS. 7 and 8 illustrate a cross-section of a portion of a system 550having a base instrument 552 and a removable cartridge 554 that areoperably engaged along a system interface 556. The base instrument 552and the removable cartridge 554 may be similar to the base instrument502 and the removable cartridge 504, respectively, shown in FIGS. 5 and6 . The base instrument 552 has a valve actuator 590 having an elongatedbody 592, such as a nozzle, that clears a control side 594 of the baseinstrument 552 and is inserted into an access opening 596 of a matingside 598 of the removable cartridge 554. The valve actuator 590 extendsthrough the system interface 556. Optionally, the base instrument 552may include a sealing member 595, such as an O-ring, that surrounds theelongated body 592 and seals the access opening 596 to provide a closedchamber. In an exemplary embodiment, the removable cartridge 554includes a channel valve 580, which may be a flexible membrane, that ispneumatically activated by the valve actuator 590. More specifically,the valve actuator 590 is configured to provide a fluid (e.g., air) toincrease a pressure within the closed chamber thereby causing thechannel valve 580 to deform. When the channel valve 580 is deformed, thechannel valve may cover a first port 582 of a sample channel 576 therebyblocking flow through the sample channel 576.

FIGS. 9-10 illustrate a system 600 that is similar to the systems 500and 550. More specifically, FIGS. 9 and 10 illustrate a system 600having a base instrument 602 and a removable cartridge 604 that areoperably engaged along a system interface 606. The removable cartridge604 includes a movable valve 630 that is rotatably engaged by a valveactuator 640 of the base instrument 602. The movable valve 630 is aplanar body that is shaped to permit flow through a sample channel 626when in a first rotational position (shown in FIG. 9 ) and block flowthrough the sample channel 626 when in a second rotational position(shown in FIG. 10 ). More specifically, the movable valve 630 may covera port 632 when in the second rotational position.

FIG. 11 is a perspective view of an exposed portion of a removablecartridge 700 having a microfluidic body 702 and a rotatable valve 704.The removable cartridge 700 may be similar to the removable cartridge104 (FIG. 1 ) and other removable cartridges described herein. Therotatable valve 704 may be similar to the movable valve 123 (FIG. 1 ).The rotatable valve 704 is configured to be rotatably mounted to a bodyside or surface 706 of the microfluidic body 702. The rotatable valve704 has a fluidic side 708 that is configured to slidably engage thebody side 706 when rotated about an axis 710. The microfluidic body 702may include a fluidic network 760 having a plurality of sample channels763, 764, a plurality of reservoir channels 765, and a feed channel 766.The channels 763-766 are discrete channels. For example, the channels763-766 are capable of being disconnected based on a rotational positionof the rotatable valve 704.

The channels 763-766 have corresponding ports that open to the body side706. In the illustrated embodiment, four sample channels 763 are in flowcommunication with a single sample channel 764. As such, the samplechannels 763 may be referred to as channel portions, and the samplechannel 764 may be referred to as a common sample channel. Each of thesample channels 763 is operably coupled to a pair of channel valves 761,762. The channel valves 761, 762 may be similar to the channel valvesdescribed herein, such as the channel valve 530. When in correspondingclosed positions, the channel valves 761, 762 may seal a liquidcontaining a corresponding biological sample. In some embodiments, thesample channels 763 extend adjacent to a thermal-control area 770. Whenthe biological samples are sealed within the corresponding samplechannels 763, a heating element (not shown) and a thermal block (notshown) may be positioned adjacent to the thermal-control area 770. Theheating element and the thermal block may coordinate to increase and/ordecrease a temperature experienced by the biological samples within thesample channels 763. In such embodiments, the sample channels 763 mayconstitute sample-preparation regions.

The feed channel 766 is in flow communication with a reaction chamber716, and the reservoir channels 765 may be in flow communication withcorresponding reservoirs (not shown) of a storage module (not shown).The sample channel 764 has a network port 721, the feed channel 766 hasa feed port 722, and the reservoir channels 765 have correspondingreservoir ports 723. The network port 721, the feed port 722, and thereservoir ports 723 open to the body side 706. The reservoir ports 723are in flow communication with corresponding module ports 724 throughthe corresponding reservoir channel 765. As shown, the module ports 724may be positioned at various locations along the body side 706 away fromfeed port 722 or the axis 710. The module ports 724 are configured tofluidically couple to the reservoirs (not shown). The module ports 724may have locations that are based on sizes of the reservoirs.

In the illustrated embodiment, the microfluidic body 702 has a total offifteen channels that directly interconnect to the rotatable valve 704.More specifically, only one sample channel 764 and only one feed channel766, but thirteen reservoir channels 765 may directly interconnect(fluidically) to the rotatable valve 704. In other embodiments, themicrofluidic body 702 may include multiple sample channels 764 and/ormultiple feed channels 766 that directly interconnect with the rotatablevalve 704. Each of the sample channels 763 may be fluidically coupled toa corresponding sample port (not shown) that is configured to receive abiological sample from the user.

The fluidic side 708 is configured to slidably engage the body side 706at a valve-receiving area 728. The rotatable valve 704 is sized andshaped such that the fluidic side 708 covers the valve-receiving area728 and one or more of the ports 721-723 along the body side 706. Therotatable valve 704 includes a flow channel 744 (shown in FIG. 12 ) thatis configured to fluidically interconnect the feed port 722 to one ormore of the ports 721, 723. The rotatable valve 704 may block flowthrough one or more ports and permit flow through one or more otherports based on a position and a configuration of the rotatable valve704.

FIG. 12 illustrates a cross-section of the rotatable valve 704 that isoperably engaged with a valve actuator 730. More specifically, therotatable valve 704 includes a valve body 732 having the fluidic side708 and an operative side 734. The operative side 734 may include amechanical interface 736 that is configured to engage the valve actuator730. In the illustrated embodiment, the mechanical interface 736includes a planar body or fin that coincides with the axis 710. Thevalve actuator 730 includes a slot 738 that is configured to receive themechanical interface 736 such that the valve actuator 730 operablyengages the rotatable valve 704. More specifically, the valve actuator730 may engage the rotatable valve 704 so that the valve actuator 730 iscapable of rotating the rotatable valve 704 about the axis 710.

The fluidic side 708 includes a plurality of valve ports 740, 742 and aflow channel 744 extending between the valve ports 740, 742. The fluidicside 708 is slidably engaged to the body surface 706 at thevalve-receiving area 728. In an exemplary embodiment, the rotatablevalve 704 includes only two valve ports 740, 742 and only one flowchannel 744. In other embodiments, the rotatable valve 704 may includemore than two valve ports and/or more than one flow channel.

As shown in FIG. 12 , the feed port 722 is fluidically aligned andcoupled to the valve port 740, and the valve port 742 is fluidicallyaligned and coupled to the network port 721. Based on the rotationalposition of the rotatable valve 704, the valve port 742 may also befluidically coupled to one of the component ports 723. As noted above,the rotatable valve 704 is configured to rotate about the axis 710. Insome embodiments, the feed port 722 and the valve port 740 arepositioned such that the feed port 722 and the valve port 740 arealigned with the axis 710. More specifically, the axis 710 extendsthrough each of the feed port 722 and the valve port 740.

When the valve actuator 730 is operably engaged to the rotatable valve704, the valve actuator 730 may apply an actuator force 748 in adirection against the body side 706. In such embodiments, the actuatorforce 748 may be sufficient to seal the flow channel 744 between thevalve ports 740, 742 and to seal the reservoir ports 723 and/or thenetwork port 721.

Accordingly, the rotatable valve 704 may fluidically couple the feedport 722 and the network port 721 at a first rotational position andfluidically couple the feed port 722 and a corresponding reservoir port723 at a second rotational position. When the rotatable valve 704 isrotated between the different rotational positions, the rotatable valve704 effectively changes a flow path of the fluidic network.

The fluid may flow in either direction through the flow channel 744. Forexample, a system pump (not shown), such as the system pump 119 (FIG. 1) may be in flow communication with the feed port 722. The system pumpmay generate a suction force that pulls the fluid through the networkport 721 (or a corresponding reservoir port 723) then into the flowchannel 744 and then through the feed port 722. Alternatively, thesystem pump may provide a positive pressure that displaces fluid withinthe flow channel 744 such that the fluid flows through the feed port 722then into the flow channel 744 and then through the network port 721 (ora corresponding reservoir port 723).

FIG. 13 is a top-down view of the body side 706 illustrating the networkport 721, the feed port 722, and the reservoir ports 723. The flowchannel 744 is represented in two different rotational positions. Thereservoir ports 723 may include reservoir ports 723A-723D. Each of thereservoir ports 723A-723D is fluidically coupled to a correspondingreservoir through the corresponding reservoir channel 765 (FIG. 10 ).More specifically, the reservoir port 723A is fluidically coupled to ahydrogenation buffer, the reservoir port 723B is fluidically coupled toa nucleotides solution, the reservoir port 723C is fluidically coupledto a wash solution, and the reservoir port 723D is fluidically coupledto a cleaving solution. As described above, based on a rotationalposition of the rotatable valve 704 (FIG. 11 ), the flow channel 744 mayfluidically couple the feed port 722 to the sample channels 763, 764 orto a corresponding reservoir.

Table 1 illustrates various stages of a sequencing-by-synthesis (SBS)protocol, but it is understood that other assay protocols may beimplemented. At stage 1, the flow channel 744 has a rotational positionthat fluidically couples the network port 721 and the feed port 722. Atstage 1, the channel valves (not shown) may be selectively activated toseal the second, third, and fourth biological samples within thecorresponding sample-preparation region, but permit the first biologicalsample to flow through the network port 721. Accordingly, at stage 1,the system pump may apply a suction force that draws the firstbiological sample into the flow channel 744. At stage 2, the rotatablevalve 704 is rotated to a second rotational position, while the firstbiological sample is stored within the flow channel 744, so that theflow channel 744 fluidically couples the reservoir port 723A and thefeed port 722. In the second rotational position, the system pump mayprovide a positive displacement force that pushes the first biologicalsample through the reservoir port 723A and into the hydrogenation bufferreservoir.

At stage 3, the rotatable valve 704 is rotated back to the firstrotational position and the channel valves are selectively activated sothat the second biological sample may be drawn into the flow channel744. At stage 4, the rotatable valve 704 is rotated back to the secondrotational position, while the first biological sample is stored withinthe flow channel 744, and the second biological sample is added to thehydrogenation buffer with the first biological sample. During stages5-8, the third and fourth biological samples are removed from thecorresponding sample-preparation regions and added to the hydrogenationbuffer. Accordingly, four biological samples may be stored within asingle reservoir having hydrogenation buffer. Reactions may occur withthe biological samples and the hydrogenation buffer that prepare thebiological samples for SBS sequencing.

At stage 9, the combined biological samples/hydrogenation buffer isdrawn through the reservoir port 723A, through the flow channel 744,through the feed port 722, and into the reaction chamber (not shown).The biological samples may be immobilized to surfaces that define thereaction chamber. For example, clusters may be formed that include thebiological samples. Stages 10-13 represent a sequencing cycle. At stage10, the rotatable valve 704 may be at a third rotational position sothat a nucleotides solution may be drawn through the flow channel 744and into the reaction chamber. At such time, a base may be incorporatedinto the corresponding biological samples (e.g., template nucleicacids). At stage 11, the rotatable valve 704 may be at a fourthrotational position so that a wash solution may flow through thereaction chamber and carry the nucleotides solution away from thereaction chamber. After stage 11, the reaction chamber may be imaged bythe imaging detector. The color of light emitted from the clusters maybe used to identify the bases incorporated by the clusters. At stage 12,the rotatable valve 704 may be at a fourth rotational position so that acleaving solution may flow through the reaction chamber and thefluorophores (and, if present, reversible terminator moieties) may beremoved from the clusters. At stage 13, the rotatable valve 704 may beat the third rotational position again and the wash solution may flowthrough the reaction chamber to remove the cleaving solution. Stages10-13 may be repeated until completion of the sequencing and/or untilreagents are depleted.

TABLE 1 Type of Fluid Flowing into Flow Port Channel Flow DirectionStage 1 721 1st Biological Sample Downstream Stage 2 723A 1st BiologicalSample Upstream Stage 3 721 2nd Biological Sample Downstream Stage 4723A 2nd Biological Sample Upstream Stage 5 721 3rd Biological SampleDownstream Stage 6 723A 3rd Biological Sample Upstream Stage 7 721 4thBiological Sample Downstream Stage 8 723A 4th Biological Sample UpstreamStage 9 723A Combined Biological Samples + Downstream HydrogenationBuffer Stage 10 723B Nucleotides Solution Downstream Stage 11 723C WashSolution Downstream Stage 12 723D Cleaving Solution Downstream Stage 13723C Wash Solution Downstream Repeat Stages 10-13 until detectioncomplete

The above-mentioned embodiments may be used in conjunction with thesubject matter of U.S. Provisional Patent Application No. 61/951,462(hereinafter the “'462 application”), which is incorporated herein byreference in its entirety. At least a portion of the '462 Application isprovided below.

The methods described herein can be used in conjunction with a varietyof nucleic acid sequencing techniques. Particularly applicabletechniques are those wherein nucleic acids are attached at fixedlocations in an array such that their relative positions do not changeand wherein the array is repeatedly detected or imaged. Embodiments inwhich images are obtained in different color channels, for example,coinciding with different labels used to distinguish one nucleotide basetype from another are particularly applicable. In some embodiments, theprocess to determine the nucleotide sequence of a target nucleic acidcan be an automated process. Preferred embodiments includesequencing-by-synthesis (“SBS”) techniques.

“Sequencing-by-synthesis (“SBS”) techniques” generally involve theenzymatic extension of a nascent nucleic acid strand through theiterative addition of nucleotides against a template strand. Intraditional methods of SBS, a single nucleotide monomer may be providedto a target nucleotide in the presence of a polymerase in each delivery.However, in the methods described herein, more than one type ofnucleotide monomer can be provided to a target nucleic acid in thepresence of a polymerase in a delivery.

SBS can utilize nucleotide monomers that have a terminator moiety orthose that lack any terminator moieties. Methods utilizing nucleotidemonomers lacking terminators include, for example, pyrosequencing andsequencing using gamma-phosphate-labeled nucleotides, as set forth infurther detail below. In methods using nucleotide monomers lackingterminators, the number of nucleotides added in each cycle is generallyvariable and dependent upon the template sequence and the mode ofnucleotide delivery. For SBS techniques that utilize nucleotide monomershaving a terminator moiety, the terminator can be effectivelyirreversible under the sequencing conditions used as is the case fortraditional Sanger sequencing which utilizes dideoxynucleotides, or theterminator can be reversible as is the case for sequencing methodsdeveloped by Solexa (now Illumina, Inc.).

SBS techniques can utilize nucleotide monomers that have a label moietyor those that lack a label moiety. Accordingly, incorporation events canbe detected based on a characteristic of the label, such as fluorescenceof the label; a characteristic of the nucleotide monomer such asmolecular weight or charge; a byproduct of incorporation of thenucleotide, such as release of a proton or pyrophosphate; or the like.In embodiments, where two or more different nucleotides are present in asequencing reagent, the different nucleotides can be distinguishablefrom each other, or alternatively, the two or more different labels canbe the indistinguishable under the detection techniques being used. Forexample, the different nucleotides present in a sequencing reagent canhave different labels and they can be distinguished using appropriateoptics as exemplified by the sequencing methods developed by Solexa (nowIllumina, Inc.).

In another exemplary type of SBS, cycle sequencing is accomplished bystepwise addition of reversible terminator nucleotides containing, forexample, a cleavable or photobleachable dye label as described, forexample, in International Patent Pub. No. WO 04/018497 and U.S. Pat. No.7,057,026, the disclosures of which are incorporated herein byreference. This approach is being commercialized by Illumina Inc., andis also described in International Patent Pub. No. WO 91/06678 andInternational Patent Pub. No. WO 07/123,744, each of which isincorporated herein by reference. The availability offluorescently-labeled terminators in which both the termination can bereversed and the fluorescent label cleaved facilitates efficient cyclicreversible termination (CRT) sequencing. Polymerases can also beco-engineered to efficiently incorporate and extend from these modifiednucleotides.

Preferably in reversible terminator-based sequencing embodiments, thelabels do not substantially inhibit extension under SBS reactionconditions. However, the detection labels can be removable, for example,by cleavage or degradation. Images can be captured followingincorporation of labels into arrayed nucleic acid features. Inparticular embodiments, each cycle involves simultaneous delivery offour different nucleotide types to the array and each nucleotide typehas a spectrally distinct label. Four images can then be obtained, eachusing a detection channel that is selective for one of the fourdifferent labels. Alternatively, different nucleotide types can be addedsequentially and an image of the array can be obtained between eachaddition step. In such embodiments each image will show nucleic acidfeatures that have incorporated nucleotides of a particular type.Different features will be present or absent in the different images duethe different sequence content of each feature. However, the relativeposition of the features will remain unchanged in the images. Imagesobtained from such reversible terminator-SBS methods can be stored,processed and/or analyzed as set forth herein. Following the imagecapture step, labels can be removed and reversible terminator moietiescan be removed for subsequent cycles of nucleotide addition anddetection. Removal of the labels after they have been detected in aparticular cycle and prior to a subsequent cycle can provide theadvantage of reducing background signal and crosstalk between cycles.Examples of useful labels and removal methods are set forth below.

In particular embodiments some or all of the nucleotide monomers caninclude reversible terminators. In such embodiments, reversibleterminators/cleavable fluors can include fluor linked to the ribosemoiety via a 3′ ester linkage (Metzker, Genome Res. 15:1767-1776 (2005),which is incorporated herein by reference). Other approaches haveseparated the terminator chemistry from the cleavage of the fluorescencelabel (Ruparel et al., Proc Natl Acad Sci USA 102: 5932-7 (2005), whichis incorporated herein by reference in its entirety). Ruparel et aldescribed the development of reversible terminators that used a small 3′allyl group to block extension, but could easily be deblocked by a shorttreatment with a palladium catalyst. The fluorophore was attached to thebase via a photocleavable linker that could easily be cleaved by a 30second exposure to long wavelength UV light. Thus, either disulfidereduction or photocleavage can be used as a cleavable linker. Anotherapproach to reversible termination is the use of natural terminationthat ensues after placement of a bulky dye on a dNTP. The presence of acharged bulky dye on the dNTP can act as an effective terminator throughsteric and/or electrostatic hindrance. The presence of one incorporationevent prevents further incorporations unless the dye is removed.Cleavage of the dye removes the fluor and effectively reverses thetermination. Examples of modified nucleotides are also described in U.S.Pat. Nos. 7,427,673, and 7,057,026, the disclosures of which areincorporated herein by reference in their entireties.

Additional exemplary SBS systems and methods which can be utilized withthe methods and systems described herein are described in U.S. PatentPub. No. 2007/0166705, U.S. Patent Pub. No. 2006/0188901, U.S. Pat. No.7,057,026, U.S. Patent Pub. No. 2006/0240439, U.S. U.S. Patent Pub. No.2006/0281109, International Patent Pub. No. WO 05/065814, U.S. PatentPub. No. 2005/0100900, International Patent Pub. No. WO 06/064199,International Patent Pub. No. WO 07/010,251, U.S. U.S. Patent Pub. No.2012/0270305 and U.S. Patent Pub. No. 2013/0260372, the disclosures ofwhich are incorporated herein by reference in their entireties.

Some embodiments can utilize detection of four different nucleotidesusing fewer than four different labels. For example, SBS can beperformed utilizing methods and systems described in the incorporatedmaterials of U.S. Patent Pub. No. 2013/0079232. As a first example, apair of nucleotide types can be detected at the same wavelength, butdistinguished based on a difference in intensity for one member of thepair compared to the other, or based on a change to one member of thepair (e.g., via chemical modification, photochemical modification orphysical modification) that causes apparent signal to appear ordisappear compared to the signal detected for the other member of thepair. As a second example, three of four different nucleotide types canbe detected under particular conditions while a fourth “dark-state”nucleotide type lacks a label that is detectable under those conditions,or is minimally detected under those conditions (e.g., minimal detectiondue to background fluorescence, etc). Incorporation of the first threenucleotide types into a nucleic acid can be determined based on presenceof their respective signals and incorporation of the fourth nucleotidetype into the nucleic acid can be determined based on absence or minimaldetection of any signal. As a third example, one nucleotide type caninclude label(s) that are detected in two different channels, whereasother nucleotide types are detected in no more than one of the channels.The aforementioned three exemplary configurations are not consideredmutually exclusive and can be used in various combinations. An exemplaryembodiment that combines all three examples, is a fluorescent-based SBSmethod that uses a first nucleotide type that is detected in a firstchannel (e.g., dATP having a label that is detected in the first channelwhen excited by a first excitation wavelength), a second nucleotide typethat is detected in a second channel (e.g., dCTP having a label that isdetected in the second channel when excited by a second excitationwavelength), a third nucleotide type that is detected in both the firstand the second channel (e.g., dTTP having at least one label that isdetected in both channels when excited by the first and/or secondexcitation wavelength) and a fourth nucleotide type that lacks a labelthat is not, or minimally, detected in either channel (e.g., dGTP havingno label).

Further, as described in the incorporated materials of U.S. Patent Pub.No. 2013/0079232, sequencing data can be obtained using a singlechannel. In such so-called one-dye sequencing approaches, the firstnucleotide type is labeled but the label is removed after the firstimage is generated, and the second nucleotide type is labeled only aftera first image is generated. The third nucleotide type retains its labelin both the first and second images, and the fourth nucleotide typeremains unlabeled in both images.

Some embodiments can utilize sequencing by ligation techniques. Suchtechniques utilize DNA ligase to incorporate oligonucleotides andidentify the incorporation of such oligonucleotides. Theoligonucleotides typically have different labels that are correlatedwith the identity of a particular nucleotide in a sequence to which theoligonucleotides hybridize. As with other SBS methods, images can beobtained following treatment of an array of nucleic acid features withthe labeled sequencing reagents. Each image will show nucleic acidfeatures that have incorporated labels of a particular type. Differentfeatures will be present or absent in the different images due thedifferent sequence content of each feature, but the relative position ofthe features will remain unchanged in the images. Images obtained fromligation-based sequencing methods can be stored, processed and analyzedas set forth herein. Exemplary sequencing systems and methods which canbe utilized with the methods and systems described herein are describedin U.S. Pat. Nos. 6,969,488, 6,172,218, and 6,306,597, the disclosuresof which are incorporated herein by reference in their entireties.

Some embodiments can utilize nanopore sequencing (Deamer, D. W. &Akeson, M. “Nanopores and nucleic acids: prospects for ultrarapidsequencing.” Trends Biotechnol. 18, 147-151 (2000); Deamer, D. and D.Branton, “Characterization of nucleic acids by nanopore analysis”. Acc.Chem. Res. 35:817-825 (2002); Li, J., M. Gershow, D. Stein, E. Brandin,and J. A. Golovchenko, “DNA molecules and configurations in asolid-state nanopore microscope” Nat. Mater. 2:611-615 (2003), thedisclosures of which are incorporated herein by reference in theirentireties). In such embodiments, the target nucleic acid passes througha nanopore. The nanopore can be a synthetic pore or biological membraneprotein, such as alpha-hemolysin. As the target nucleic acid passesthrough the nanopore, each base-pair can be identified by measuringfluctuations in the electrical conductance of the pore. (U.S. Pat. No.7,001,792; Soni, G. V. & Meller, “A. Progress toward ultrafast DNAsequencing using solid-state nanopores.” Clin. Chem. 53, 1996-2001(2007); Healy, K. “Nanopore-based single-molecule DNA analysis.”Nanomed. 2, 459-481 (2007); Cockroft, S. L., Chu, J., Amorin, M. &Ghadiri, M. R. “A single-molecule nanopore device detects DNA polymeraseactivity with single-nucleotide resolution.” J. Am. Chem. Soc. 130,818-820 (2008), the disclosures of which are incorporated herein byreference in their entireties). In other embodiments, an endonucleasecan be coupled with a nanopore such that nucleotides releasedsequentially from an end of the nucleic acid by endonuclease aredetected when they pass through the nanopore. Each nucleotide can bedistinguished based on the different base moieties or based on addedmoieties. Data obtained from nanopore sequencing can be stored,processed and analyzed as set forth herein. In particular, the data canbe treated as an image in accordance with the exemplary treatment ofoptical images and other images that is set forth herein.

Some embodiments can utilize methods involving the real-time monitoringof DNA polymerase activity. Nucleotide incorporations can be detectedthrough fluorescence resonance energy transfer (FRET) interactionsbetween a fluorophore-bearing polymerase and gamma-phosphate-labelednucleotides as described, for example, in U.S. Pat. Nos. 7,329,492 and7,211,414 (each of which is incorporated herein by reference) ornucleotide incorporations can be detected with zero-mode waveguides asdescribed, for example, in U.S. Pat. No. 7,315,019 (which isincorporated herein by reference) and using fluorescent nucleotideanalogs and engineered polymerases as described, for example, in U.S.Pat. No. 7,405,281 and U.S. Patent Pub. No. 2008/0108082 (each of whichis incorporated herein by reference). The illumination can be restrictedto a zeptoliter-scale volume around a surface-tethered polymerase suchthat incorporation of fluorescently labeled nucleotides can be observedwith low background (Levene, M. J. et al. “Zero-mode waveguides forsingle-molecule analysis at high concentrations.” Science 299, 682-686(2003); Lundquist, P. M. et al. “Parallel confocal detection of singlemolecules in real time.” Opt. Lett. 33, 1026-1028 (2008); Korlach, J. etal. “Selective aluminum passivation for targeted immobilization ofsingle DNA polymerase molecules in zero-mode waveguide nano structures.”Proc. Natl. Acad. Sci. USA 105, 1176-1181 (2008), the disclosures ofwhich are incorporated herein by reference in their entireties). Imagesobtained from such methods can be stored, processed and analyzed as setforth herein.

Some SBS embodiments include detection of a proton released uponincorporation of a nucleotide into an extension product. For example,sequencing based on detection of released protons can use an electricaldetector and associated techniques that are commercially available fromIon Torrent (Guilford, Conn., a Life Technologies subsidiary) orsequencing methods and systems described in U.S. Patent Pub. No.2009/0026082; U.S. Patent Pub. No. 2009/0127589; U.S. Patent Pub. No.2010/0137143; or U.S. Patent Pub. No. 2010/0282617, each of which isincorporated herein by reference.

The above SBS methods can be advantageously carried out in multiplexformats such that multiple different target nucleic acids aremanipulated simultaneously. In particular embodiments, different targetnucleic acids can be treated in a common reaction vessel or on a surfaceof a particular substrate. This allows convenient delivery of sequencingreagents, removal of unreacted reagents and detection of incorporationevents in a multiplex manner. In embodiments using surface-bound targetnucleic acids, the target nucleic acids can be in an array format. In anarray format, the target nucleic acids can be typically bound to asurface in a spatially distinguishable manner. The target nucleic acidscan be bound by direct covalent attachment, attachment to a bead orother particle or binding to a polymerase or other molecule that isattached to the surface. The array can include a single copy of a targetnucleic acid at each site (also referred to as a feature) or multiplecopies having the same sequence can be present at each site or feature.Multiple copies can be produced by amplification methods such as, bridgeamplification or emulsion PCR as described in further detail below.

The methods set forth herein can use arrays having features at any of avariety of densities including, for example, at least about 10features/cm², 100 features/cm², 500 features/cm², 1,000 features/cm²,5,000 features/cm², 10,000 features/cm², 50,000 features/cm², 100,000features/cm², 1,000,000 features/cm², 5,000,000 features/cm², or higher.The methods and apparatus set forth herein can include detectioncomponents or devices having a resolution that is at least sufficient toresolve individual features at one or more of these exemplifieddensities.

An advantage of the methods set forth herein is that they provide forrapid and efficient detection of a plurality of target nucleic acids inparallel. Accordingly the present disclosure provides integrated systemscapable of preparing and detecting nucleic acids using techniques knownin the art such as those exemplified above. Thus, an integrated systemof the present disclosure can include fluidic components capable ofdelivering amplification reagents and/or sequencing reagents to one ormore immobilized DNA fragments, the system comprising components such aspumps, valves, reservoirs, fluidic lines and the like. A flow cell canbe configured and/or used in an integrated system for detection oftarget nucleic acids. Exemplary flow cells are described, for example,in U.S. Patent Pub. No. 2010/0111768 A1 and U.S. patent application Ser.No. 13/273,666, each of which is incorporated herein by reference. Asexemplified for flow cells, one or more of the fluidic components of anintegrated system can be used for an amplification method and for adetection method. Taking a nucleic acid sequencing embodiment as anexample, one or more of the fluidic components of an integrated systemcan be used for an amplification method set forth herein and for thedelivery of sequencing reagents in a sequencing method such as thoseexemplified above. Alternatively, an integrated system can includeseparate fluidic systems to carry out amplification methods and to carryout detection methods. Examples of integrated sequencing systems thatare capable of creating amplified nucleic acids and also determining thesequence of the nucleic acids include, without limitation, the MiSeq™ orNextSeg™ platform (Illumina, Inc., San Diego, Calif.) or devicesdescribed in U.S. Pat. App. Pub. Nos. 2012/0270305 A1 or 2013/0260372A1, each of which is incorporated herein by reference.

“Activity detector” means any device or component that is capable ofdetecting the activity that is indicative of a particular reaction orprocess. An activity detector may be able detect predetermined events,properties, qualities, or characteristics within a predefined volume orarea. For example, an activity detector may be able to capture an imageof the predefined volume or area. An activity detector may be abledetect an ion concentration within a predefined volume of a solution oralong a predefined area. Exemplary activity detectors includecharged-coupled devices (CCD's) (e.g., CCD cameras); photomultipliertubes (PMT's); molecular characterization devices or detectors, such asthose used with nanopores; microcircuit arrangements, such as thosedescribed in U.S. Pat. No. 7,595,883, which is incorporated herein byreference in the entirety; and CMOS-fabricated sensors having fieldeffect transistors (FET's), including chemically sensitive field effecttransistors (chemFET), ion-sensitive field effect transistors (ISFET),and/or metal oxide semiconductor field effect transistors (MOSFET).Exemplary activity detectors are described, for example, inInternational Patent Pub. No. WO2012/058095.

The term “Biosensor” includes any structure having a plurality ofreaction sites. A biosensor may include a solid-state imaging device(e.g., CCD or CMOS imager) and, optionally, a flow cell mounted thereto.The flow cell may include at least one flow channel that is in fluidcommunication with the reaction sites. As one specific example, thebiosensor is configured to fluidicly and electrically couple to abioassay system. The bioassay system may deliver reactants to thereaction sites according to a predetermined protocol (e.g.,sequencing-by-synthesis) and perform a plurality of imaging events. Forexample, the bioassay system may direct solutions to flow along thereaction sites. At least one of the solutions may include four types ofnucleotides having the same or different fluorescent labels. Thenucleotides may bind to corresponding oligonucleotides located at thereaction sites. The bioassay system may then illuminate the reactionsites using an excitation light source (e.g., solid-state light sources,such as light-emitting diodes or LEDs). The excitation light may have apredetermined wavelength or wavelengths, including a range ofwavelengths. The excited fluorescent labels provide emission signalsthat may be detected by the light detectors.

In one aspect, the solid-state imager includes a CMOS image sensorcomprising an array of light detectors that are configured to detect theemission signals. In some embodiments, each of the light detectors hasonly a single pixel and a ratio of the pixels to the detection pathsdefined by the filter walls can be substantially one-to-one. Exemplarybiosensors are described, for example, in U.S. patent application Ser.No. 13/833,619.

“Detection surface” means any surface that includes an optical detector.The detector can be based upon any suitable technology, such as thoseincluding a charge coupled device (CCD) or a complementarymetal-oxide-semiconductor (CMOS). In particular embodiments a CMOSimager having a single-photon avalanche diode (CMOS-SPAD) can be used,for example, to distinguish fluorophores using fluorescence lifetimeimaging (FLIM). Exemplary CMOS based systems that can be used for FLIMare described in U.S. Patent Pub. No. 2008/0037008 A1; Giraud et al.,Biomedical Optics Express 1: 1302-1308 (2010); or Stoppa et al., IEEEEuropean Solid-State Device Conference (ESSCIRC), Athens, Greece, IEEE,pp. 204-207 (2009), each of which is incorporated herein by reference inits entirety. Other useful detection devices that can be used include,for example, those described in U.S. Pat. No. 7,329,860 and U.S. PatentPub. No. 2010/0111768, each of which is incorporated herein by referencein its entirety.

In addition, it will be appreciated that other signal detecting devicesas known in the art can be used to detect signals produced in a methodset forth herein. For example detectors used to detect pyrophosphate orprotons are particularly useful. Pyrophosphate release can be detectedusing detectors such as those commercially available from 454 LifeSciences (Branford, Conn., a Roche Company) or described in U.S. PatentPub. No. 2005/0244870, which is incorporated herein by reference in itsentirety. Exemplary systems for detecting primer extension based onproton release include those that are commercially available from IonTorrent (Guilford, Conn., a ThermoFisher subsidiary) or described inU.S. Patent Pub. Nos. 2009/0026082; 2009/0127589; 2010/0137143; and2010/0282617, each of which is incorporated herein by reference in itsentirety. Exemplary detection surfaces and detectors are described, forexample, in U.S. Patent Pub. No. 2013/0116128A1, which is incorporatedherein by reference.

“Sequencing module” means a CMOS chip that has been adapted forsequencing applications. The module can comprise a surface comprising asubstrate of hydrophilic regions for nucleic acid attachment andamplification surrounded by hydrophobic regions. For example, dynamicpads having a hydrophilic patch, such as those described above, can beused. Alternatively or additionally, a collection of dynamic padsincluding some that are in a hydrophilic state while surrounding padsare in a hydrophobic state can form a hydrophilic regions surrounded bya hydrophobic region. The surface for nucleic acid attachment wouldoptionally comprise a plurality of isolated regions such that eachisolated region contains a plurality of nucleic acid molecules that ispreferably derived from one nucleic acid molecule for sequencing. Forexample, the hydrophilic region can include a gel. The hydrophilicregions could be smooth, textured, porous, non-porous, etc. Thehydrophobic regions are preferably located between the hydrophilicregions. Reagents move across the surface by way of any number offorces.

The subject matter described herein includes, in one or moreembodiments, a disposable, integrated microfluidic cartridge and methodsof making and using same. The method of making the disposable,integrated microfluidic cartridge optionally utilizes a flexible printedcircuit board (PCB) and roll-2-roll (R2R) printed electronics for themonolithic integration of CMOS technology and digital fluidics. Namely,the disposable, integrated microfluidic cartridge includes a stack offluidics layers in which a CMOS sensor is integrated, all installed in ahousing. Accordingly, conventional injection molded fluidics can beintegrated with flexible PCB technology. The fluidics layers are formedusing materials that suitable for use in a R2R printed electronicsprocess. Further, the fluidics layers include a polymerase chainreaction (PCR) region and a reagent mixing and distribution region. Thefluidics layers also include a set of membrane valves by which the PCRregion can be completely sealed off.

The method of using the disposable, integrated microfluidic cartridgeincludes performing multiplex PCR and downstream mixing needed forsequencing.

Embodiments set forth herein include a CMOS flow cell, wherein most orup to about 100% of the biosensor active area is accessible for reagentdelivery and illumination.

FIG. 14 illustrates a flow diagram of an example of a method 100 ofusing a flexible printed circuit board (PCB) and roll-2-roll (R2R)printed electronics for the monolithic integration of CMOS technologyand digital fluidics. Namely, using method 100, multilayer laminatedfluidics can be integrated with flexible PCB technology (see FIG. 15 ).Further, using the structure formed using method 100, conventionalinjection molded fluidics can be integrated with flexible PCB technology(see FIGS. 26 through 45 ). Method 100 may include, but is not limitedto, the following steps.

At a step 110, the fluidic layers are formed and then laminated andbonded together. For example, FIG. 15 illustrates an exploded view of aset of fluidics layers 200 that can be laminated and bonded together inthis step. In this example, fluidics layers 200 comprises, in order, aninlet/outlet ports layer 210, a fluidics channels layer 220, a flexiblePCB layer 260, a sequencing chamber bottom layer 280, a sequencingchamber layer 250, and a membrane layer 240 that is coplanar with asequencing chamber top layer 290. Inlet/outlet ports layer 210, fluidicschannels layer 220, flexible PCB layer 260, sequencing chamber bottomlayer 280, sequencing chamber layer 250, membrane layer 240, andsequencing chamber top layer 290 are suitable for forming using a R2Rprinted electronics process.

Inlet/outlet ports layer 210 can be formed of, for example,polycarbonate, poly(methyl methacrylate) (PMMA), cyclic olefin copolymer(COC), and/or polyimide. Inlet/outlet ports layer 210 can be from about25 μm to about 1000 μm thick in one example, or is about 250 μm thick inanother example. An arrangement of openings (or holes) is provided ininlet/outlet ports layer 210. The openings (or holes) provide fluidpaths the can serve as inlet ports and/or outlet ports to, for example,various liquid supply reservoirs (not shown). More details ofinlet/outlet ports layer 210 are shown and described herein below withreference to FIGS. 55A and 55B.

Fluidics channels layer 220 can be formed of, for example,polycarbonate, PMMA, COC, and/or polyimide. Fluidics channels layer 220can be from about 25 μm to about 1000 μm thick in one example, or isabout 250 μm thick in another example. An arrangement of fluidicschannels is provided in fluidics channels layer 220. The fluidicschannels provide fluid paths from one destination to another alongfluidics layers 200. Because fluidics channels layer 220 is sandwichedbetween inlet/outlet ports layer 210 and flexible PCB layer 260, fluidcan be confined within the fluidics channels by inlet/outlet ports layer210 on the bottom and by flexible PCB layer 260 on the top. In oneexample, fluidics channels layer 220 is used to perform PCR anddownstream mixing needed for sequencing. More details of fluidicschannels layer 220 are shown and described herein below with referenceto FIGS. 56A and 56B.

Flexible PCB layer 260 can be formed of, for example, polycarbonate,PMMA, COC, and/or polyimide. Flexible PCB layer 260 can be from about 30μm to about 300 μm thick in one example, or is about 200 μm thick inanother example. An arrangement of openings (or holes) is provided inflexible PCB layer 260. The openings (or holes) provide fluid paths thecan serve as inlets and/or outlets of membrane valves that are used tocontrol the flow of liquid in the fluidics channels of fluidics channelslayer 220. More details of flexible PCB layer 260 are shown anddescribed herein below with reference to FIGS. 57A and 57B.

Sequencing chamber bottom layer 280 can be formed of, for example,polycarbonate, PMMA, COC, and/or polyimide. Sequencing chamber bottomlayer 280 can be from about 25 μm to about 1000 μm thick in one example,or is about 250 μm thick in another example. An arrangement of openingsis provided in sequencing chamber bottom layer 280 for forming themembrane valves within the stack of fluidics layers 200. Sequencingchamber bottom layer 280 also includes a CMOS device, such as a CMOSimage sensor 262, that is located in proximity to the sequencing chamberof sequencing chamber layer 250. Sequencing chamber bottom layer 280 iscoplanar with the CMOS device and acts as the fluid connecting layer tothe inlet/outlet of the sequencing chamber of sequencing chamber layer250. More details of sequencing chamber bottom layer 280 can are shownand described herein below with reference to FIGS. 58A and 58B.

Sequencing chamber layer 250 can be formed of, for example,polycarbonate, PMMA, COC, and/or polyimide. Sequencing chamber layer 250can be from about 50 μm to about 300 μm thick in one example, or isabout 100 μm thick in another example. An arrangement of openings isprovided in sequencing chamber layer 250 for forming the membrane valveswithin the stack of fluidics layers 200. Sequencing chamber layer 250also includes a sequencing chamber. More details of sequencing chamberlayer 250 are shown and described herein below with reference to FIGS.59A and 59B.

Membrane layer 240 can be formed of, for example, silicone elastomer.Membrane layer 240 can be from about 25 μm to about 1000 μm thick in oneexample, or is about 250 μm thick in another example. Membrane layer 240serves as the elastic membrane for opening and closing the membranevalves within the stack of fluidics layers 200, wherein the membranevalves are created by the combination of, in order, flexible PCB layer260, sequencing chamber bottom layer 280, sequencing chamber layer 250,and membrane layer 240. More details of membrane valves are shown anddescribed herein below with reference to FIGS. 22A, 22B, 23A and 23B.More details of membrane layer 240 are shown and described herein belowwith reference to FIGS. 60A and 60B.

Sequencing chamber top layer 290 is formed of a low auto-fluorescentmaterial that has good optical properties, such as COC. Sequencingchamber top layer 290 can be from about 25 μm to about 1000 μm thick inone example, or is about 250 μm thick in another example. Sequencingchamber top layer 290 is used to cover the sequencing chamber insequencing chamber layer 250. More details of sequencing chamber toplayer 290 are shown and described herein below with reference to FIGS.60A and 60B.

Referring now again to FIG. 14 , at a step 115, a CMOS device isattached to the flexible PCB. For example, a CMOS image sensor 262 (seeFIG. 15 ) is attached to sequencing chamber bottom layer 280 of fluidicslayers 200. FIG. 16 illustrates a perspective view of an example of CMOSimage sensor 262. In one example, CMOS image sensor 262 is about 9200 μmlong, about 8000 μm wide, and about 800-1000 μm thick; and can haveabout 50 I/O pads. CMOS image sensor 262 can comprise a pixel array. Inone example, the pixel array is 4384×3292 pixels, with overalldimensions of 7272 μm×5761 μm. It will be understood that a CMOS die canhave a wide range of dimensions and I/O pad counts. For example, arectangular die (e.g. non-square dimensions that appear long skinny) canbe used with digital fluidics to utilize only part of the die in anygiven analytical protocol.

Continuing step 115, FIGS. 17A, 17B, 18, 19, and 20 illustrate sideviews of a structure 400, which shows an example of a process ofattaching a CMOS device to a flexible PCB. Structure 400 is a multilayerstructure. Referring now to FIG. 17A, the initial formation of structure400 begins with a flexible PCB. For example, the flexible PCB includes,in order, a polyimide layer 410, a PCB heater layer 412, a polyimidelayer 414, a PCB wiring layer 416, and a polyimide layer 418. Namely,FIG. 17 shows a flexible PCB having a PCB heater layer and a PCB wiringlayer, aka coupon foil.

Next and referring now to FIG. 17B, a low-temperature isotropicconductive adhesive (low-temp ICA) 420 is dispensed atop polyimide layer418.

Next and referring now to FIG. 18 , a CMOS device, such as CMOS imagesensor 262, is placed on the coupon foil; namely, atop low-temp ICA 420.In one example, CMOS image sensor 262 is placed atop low-temp ICA 420using a pick and place process that is well known. FIG. 18 shows I/Opads 422 of CMOS image sensor 262 are in contact with low-temp ICA 420and thereby electrically connected to PCB wiring layer 416. There areother attachment options available as well, including but not limitedto, controlled collapse/flipchip bonding, wirebonding, and the like.FIG. 18 also shows that CMOS image sensor 262 includes a biolayer 424that is facing away from polyimide layer 418. A protection film 426 canbe placed atop biolayer 424 until ready for use.

Next and referring now to FIG. 19 , a set of fluidic layers 428 isprovided atop polyimide layer 418 of the flexible PCB. Namely, alaminated polycarbonate film is provided that is coplanar to the CMOSsurface. An example of fluidic layers 428 is fluidics layers 200 shownin FIG. 15 .

Next and referring now to FIG. 20 , the flip-chip bonding of CMOS imagesensor 262 on the coupon foil is completed by dispensing under-fillepoxy adhesive 430 in the gaps around CMOS image sensor 262.

Referring now again to FIG. 14 , at a step 120, the final assembly of amicrofluidic cartridge that includes fluidic layers and CMOS device(s)integrated together is performed. For example, FIG. 21 illustrates aside view of an example of a microfluidic cartridge 800. Microfluidiccartridge 800 includes a fluidics portion 810 and a CMOS portion 812,which is based on structure 400 shown in FIG. 20 . Final assembly stepsmay include, for example, dispensing (printing) the under-fill epoxyadhesive 430, removing the protection film 426, laminating alow-temperature non-conductive adhesive 814 (e.g., UV or thermalnon-conductive adhesive) at CMOS portion 812, laminating alow-autofluorescent cyclic olefin copolymer (COC) layer 816 to CMOSportion 812 of microfluidic cartridge 800, and laminating a flexible PCBheater 818 on both sides of fluidics portion 810. In the process offorming microfluidic cartridge 800, it is critical to use a self-alignedprocess flow so that the surfaces of the CMOS device and the fluidiclayers are flush with each other.

A fluid path is formed through microfluidic cartridge 800. Namely, asample inlet 820 is provided at the input of fluidics portion 810 and anoutlet 822 is provided downstream of CMOS portion 812. Sample inlet 820supplies a PCR chamber 824. Then PCR chamber 824 supplies a reagentdistribution region 826. Then reagent distribution region 826 supplies asequencing chamber 828. Biolayer 424 of CMOS image sensor 262 isoriented toward sequencing chamber 828. Then sequencing chamber 828supplies outlet 822. Further, microfluidic cartridge 800 includescertain membrane valves 830 that control the flow of liquid in and outof PCR chamber 824.

FIGS. 22A and 22B illustrate perspective views of an example of membranevalve 830, wherein membrane valves can be integrated into, for example,fluidics layers 200. Referring now to FIG. 22A is a perspective view ofmembrane valve 830. In this example, membrane valve 830 includes, inorder, a base layer 910, a fluidics channel layer 912, and a reservoirlayer 914. Base layer 910, fluidics channel layer 912, and reservoirlayer 914 can be formed of, for example, polycarbonate, PMMA, COC,and/or polyimide. Reservoir layer 914 has a recessed region that createsa small reservoir 916 in reservoir layer 914. A membrane layer 918 isstretched across reservoir 916. Reservoir 916 has an inlet 920 and anoutlet 922, which provide a flow path to respective fluidics channels924. In order to better show the features of reservoir 916 as well asinlet 920 and outlet 922, FIG. 22B shows membrane valve 830 withoutmembrane layer 918 covering reservoir 916. Membrane layer 918 is formedof an elastomeric membrane material (e.g., silicone elastomer) that isflexible and stretchable.

FIGS. 23A and 23B each show a cross-sectional view of membrane valve 830taken along line A-A of FIG. 22A. An actuator, such as an actuator 1010,can be used to open and close membrane valve 830. For example, FIG. 23Ashows membrane valve 830 in the open state in which actuator 1010 is notengaged with membrane layer 918. By contrast, FIG. 23B shows membranevalve 830 in the closed state in which actuator 1010 is engaged withmembrane layer 918. Namely, the tip of actuator 1010 is used to push thecenter portion of membrane layer 918 against outlet 922 and therebyblocking the flow of liquid therethrough. Membrane valve 830 (i.e.,membrane valves 242, 244, and 246) can be actuated using, for example,mechanical or air actuation, such as solenoids or pneumatic pumps.

FIG. 24 illustrates a schematic diagram of an example of a microfluidiccartridge 1100 that includes both CMOS technology and digital fluidicsintegrated together. Namely, microfluidic cartridge 1100 includesfluidics layers 200 that are fluidly and operatively connected to foursample supplies 1110 (e.g., sample supplies 1110 a, 1110 b, 1110 c, 1110d), thirteen reagent supplies 1112 (e.g., reagent supplies 1112 a-1112m), and an outlet pump 1114. Fluidics layers 200 includes a PCR region270 and a reagent mixing and distribution region 275. PCR region 270includes, for example, four PCR channels 222 (e.g., PCR channels 222 a,222 b, 222 c, 222 d). The inlets of PCR channels 222 a, 222 b, 222 c,and 222 d are supplied by sample supplies 1110 a, 1110 b, 1110 c, and1110 d, respectively. Because microfluidic cartridge 1100 includes fourPCR channels 222 that are supplied by the four sample supplies 1110,microfluidic cartridge 1100 is configured for 4× sample multiplexing.

The inputs of the four PCR channels 222 are controlled using fourmembrane valves 242. Namely, the inputs of PCR channels 222 a, 222 b,222 c, and 222 d are controlled using membrane valves 242 a, 242 b, 242c, and 242 d, respectively. Similarly, the outputs of the four PCRchannels 222 are controlled using four membrane valves 244. Namely, theoutputs of PCR channels 222 a, 222 b, 222 c, and 222 d are controlledusing membrane valves 244 a, 244 b, 244 c, and 244 d, respectively. Theoutputs of the four PCR channels 222 supply a common PCR output channel224, which then supplies reagent mixing and distribution region 275. Thepresence of membrane valves 242 and membrane valves 244 in fluidicslayers 200 allow PCR region 270 to be completely sealed off.

Reagent mixing and distribution region 275 includes an arrangement ofthirteen reagent channels 226 (e.g., reagent channels 226 a-226 m).Further, the thirteen reagent channels 226 a-226 m are supplied via thethirteen reagent supplies 1112 a-1112 m, respectively. A rotatable valveassembly (not shown) is used to fluidly connect a certain PCR channel222 to a certain reagent supply 1112. In so doing, a certain PCR Mix canbe created. The rotatable valve assembly (not shown) is also used tofluidly connect a certain PCR Mix to a sequencing feed channel 228,which supplies an inlet of a sequencing chamber 258. Further, CMOS imagesensor 262 is positioned at sequencing chamber 258.

A sequencing outlet channel 230 is provided at the outlet of sequencingchamber 258. An outlet pump 1114 is fluidly and operatively connected tosequencing outlet channel 230. Outlet pump 1114 is used to providepositive or negative pressure in order to move liquid in any directionalong the flow paths of fluidics layers 200. Further, a series of threemembrane valves 246 are provided along the length of sequencing outletchannel 230. Membrane valves 242, 244, and 246 can be implementedaccording to membrane valve 830 that is shown and described in FIGS.22A, 22B, 23A, and 23C.

The three membrane valves 246 at sequencing outlet channel 230 can beused as pumps in place of or in combination with outlet pump 1114.Therefore, in one embodiment, microfluidic cartridge 1100 includesoutlet pump 1114 only and the three membrane valves 246 are omitted. Inanother embodiment, microfluidic cartridge 1100 includes the threemembrane valves 246 only and outlet pump 1114 is omitted. In yet anotherembodiment, microfluidic cartridge 1100 includes both outlet pump 1114and the three membrane valves 246. In still another embodiment,microfluidic cartridge 1100 includes any other type of pumping mechanismin place of outlet pump 1114 and/or the three membrane valves 246. Moredetails of an example of implementing microfluidic cartridge 1100 areshown and described herein below with reference to FIGS. 25 through 60B.

FIGS. 25 and 26 illustrate perspective views of a microfluidic cartridgeassembly 1200, which is one example of the physical instantiation of theintegrated microfluidic cartridge 1100 shown in FIG. 24 . Microfluidiccartridge assembly 1200 is an example of conventional injection moldedfluidics that is integrated with flexible PCB technology. In thisexample, microfluidic cartridge assembly 1200 is a multi-compartmentmicrofluidic cartridge that includes a housing 1210 fastened atop a baseplate 1212. Housing 1210 and base plate 1212 can be formed, for example,of molded plastic and fastened together via screws (see FIG. 32 ). Theoverall height of microfluidic cartridge assembly 1200 can be, forexample, from about 12 mm to about 100 mm. The overall length ofmicrofluidic cartridge assembly 1200 can be, for example, from about 100mm to about 200 mm. The overall width of microfluidic cartridge assembly1200 can be, for example, from about 100 mm to about 200 mm.

Inside of housing 1210 is a fluidics assembly 1400, which is shown inFIGS. 27A and 27B. Namely, FIGS. 27A and 27B illustrate perspectiveviews of an example of fluidics assembly 1400, which is installed inmicrofluidic cartridge assembly 1200 shown in FIGS. 25 and 28 . Fluidicsassembly 1400 is based on the integrated microfluidic cartridge 1100shown in FIG. 24 . Namely, fluidics assembly 1400 includes fluidicslayers 200 that is shown and described in FIGS. 15 and 24 . Fluidicsassembly 1400 also includes a rotatable valve assembly 1410 that isarranged with respect to the thirteen reagent channels 226 a-226 m inreagent mixing and distribution region 275 of fluidics layers 200. Thelength of fluidics layers 200 can be, for example, from about 100 mm toabout 200 mm. The width of fluidics layers 200 can be, for example, fromabout 100 mm to about 200 mm.

Further, fluidics assembly 1400 includes a flexible PCB heater 1412 thatwraps around both sides of PCR region 270 of fluidics layers 200. Twoindividually controlled heater traces are provided in flexible PCBheater 1412 such that there is one heater trace on one side of PCRregion 270 and another heater trace on the other side of PCR region 270.Flexible PCB heater 1412 is an example of the flexible PCB heater 818 ofmicrofluidic cartridge 800 shown in FIG. 21 . More details of an exampleof a heater tracer are shown and described herein below with referenceto FIGS. 28A and 28B. More details of an example of flexible PCB heater1412 are shown and described herein below with reference to FIGS. 54A,54B, and 54C.

Referring now again to FIGS. 25 and 26 , housing 1210 of microfluidiccartridge assembly 1200 also includes four sample loading ports 1214(e.g., sample loading ports 1214 a, 1214 b, 1214 c, 1214 d) thatsubstantially align with inputs of the four PCR channels 222 (e.g., PCRchannels 222 a, 222 b, 222 c, 222 d) of fluidics layers 200. Housing1210 of microfluidic cartridge assembly 1200 also includes thirteenreagent reservoirs 1216 that supply the thirteen reagent channels 226(e.g., reagent channels 226 a-226 m) of fluidics layers 200. Thethirteen reagent reservoirs 1216 can be the same size or different. Forexample, the reagent reservoirs 1216 can hold volumes of liquid rangingfrom about 0.001 ml to about 0.150 ml.

Housing 1210 of microfluidic cartridge assembly 1200 also includes awaste reservoir 1218 that is supplied by sequencing outlet channel 230.Waste reservoir 1218 can hold a volume of liquid ranging, for example,from about 25 ml to about 100 ml. FIG. 26 shows that reagent reservoirs1216 and waste reservoir 1218 may be covered and sealed with, forexample, a foil seal 1220.

FIGS. 28A and 28B illustrate a plan view and a cross-sectional view,respectively, of an example of a heater trace 1500 that can be installedin fluidics assembly 1400 shown in FIGS. 27A and 27B. Namely, FIG. 28Ashows a plan view of an example of heater trace 1500, which is has aserpentine type of layout. FIG. 28B shows a cross-sectional view of oneside of flexible PCB heater 1412 of fluidics assembly 1400, whichincludes heater trace 1500. Flexible PCB heater 1412 is a multilayerstructure that includes, for example, in order, a single-sided flexiblecopper layer 1510, an adhesive layer 1512, a dielectric layer 1514, acopper heater layer 1516 in which heater trace 1500 is patterned, and aKapton® layer 1518. Copper heater layer 1516 shows the cross-section ofheater trace 1500 taken along the line A-A of FIG. 28A.

FIGS. 29, 30, 31, 32, 33A and 33B illustrate various other views ofmicrofluidic cartridge assembly 1200 of FIG. 25 , showing more detailsthereof. Namely, FIG. 29 shows a perspective view and FIG. 30 shows aplan view of the housing 1210-side of microfluidic cartridge assembly1200, both showing more details of the configuration of the thirteenreagent reservoirs 1216 and waste reservoir 1218. FIG. 31 shows a planview of the housing 1210-side of microfluidic cartridge assembly 1200with the foil seal 1220 installed. Foil seal 1220 has an opening so thatthe four sample loading ports 1214 remain exposed and accessible.

FIG. 32 shows a perspective view of the base plate 1212-side ofmicrofluidic cartridge assembly 1200. FIG. 33A shows a plan view of thebase plate 1212-side of microfluidic cartridge assembly 1200. FIG. 33Bshows a side view of microfluidic cartridge assembly 1200. FIGS. 32,33A, and 33B show more details of base plate 1212. Namely, base plate1212 includes an opening 1222 and an opening 1224 for revealing portionsof PCR region 270 of fluidics layers 200 of fluidics assembly 1400.Shown through opening 1224 is a set of I/O pads 1226 for contactingflexible PCB heater 1412 of fluidics assembly 1400.

Along one edge of opening 1222 are four openings 1228 for accessing andactuating the four membrane valves 242 of fluidics layers 200 offluidics assembly 1400. Namely, opening 1228 a substantially aligns withmembrane valve 242 a. Opening 1228 b substantially aligns with membranevalve 242 b. Opening 1228 c substantially aligns with membrane valve 242c. Opening 1228 d substantially aligns with membrane valve 242 d.

Along the opposite edge of opening 1222 are four openings 1230 foraccessing and actuating the four membrane valves 244 of fluidics layers200 of fluidics assembly 1400. Namely, opening 1230 a substantiallyaligns with membrane valve 244 a. Opening 1230 b substantially alignswith membrane valve 244 b. Opening 1230 c substantially aligns withmembrane valve 244 c. Opening 1230 d substantially aligns with membranevalve 244 d.

Additionally, base plate 1212 includes an opening 1232 for accessing andactuating the membrane valves 246 of fluidics layers 200 of fluidicsassembly 1400. Base plate 1212 also includes an opening 1234 atsequencing chamber 258. One corner of base plate 1212 has a bevel 1236,which is used for orienting microfluidic cartridge assembly 1200 in, forexample, the instrument deck of a microfluidics system (not shown).FIGS. 32 and 33A also show four screws 1238 that are used to fasten baseplate 1212 to housing 1210. Further, rotatable valve assembly 1410 isshown with respect to reagent mixing and distribution region 275 offluidics layers 200 of fluidics assembly 1400. Rotatable valve assembly1410 includes a knob that has a grip portion 1240 by which a user or anapparatus may turn a flow controller portion 1242 (see FIG. 35 ).

Starting with microfluidic cartridge assembly 1200 oriented base plate1212-side up, FIGS. 34 through 42 essentially show a step-by-stepdeconstruction of microfluidic cartridge assembly 1200 as a means toreveal the placement and installation of the interior componentsthereof. First, FIG. 34 shows microfluidic cartridge assembly 1200 withbase plate 1212 removed in order to reveal fluidics assembly 1400. In sodoing, the flexible PCB layer 260-side of fluidics layers 200 isvisible. Further, one side of flexible PCB heater 1412 is visible. Alsorevealed is a spacer 1244 between fluidics layers 200 and base plate1212. In FIG. 34 , membrane valves 242, 244, and 246 are visible.

Referring now to FIG. 35 , grip portion 1240 of rotatable valve assembly1410 has been removed so that flow controller portion 1242 is nowvisible. The underside (not shown) of grip portion 1240 is designed toengage with flow controller portion 1242 so that flow controller portion1242 can be rotated to direct the flow of liquid through one of thethirteen reagent channels 226.

Referring now to FIG. 36 , flow controller portion 1242 of rotatablevalve assembly 1410 has been removed so that the fluid paths associatedwith PCR output channel 224, reagent channels 226, and sequencing feedchannel 228 of fluidics layers 200 are visible.

Referring now to FIG. 37 , fluidics layers 200 are shown withtransparency so that the fluid paths are visible within microfluidiccartridge assembly 1200.

Referring now to FIG. 38 , fluidics layers 200 has been removed andflexible PCB heater 1412 is shown alone within housing 1210. Referringnow to FIG. 39 , flexible PCB heater 1412 has been removed and fluidicslayers 200 are shown alone within housing 1210.

Referring now to FIG. 40 , both fluidics layers 200 and flexible PCBheater 1412 have been removed from housing 1210. In this view, the flowpaths in housing 1210 that are associated with sample loading ports1214, the thirteen reagent reservoirs 1216, and waste reservoir 1218 arevisible. For example, housing 1210 includes openings 1246 to sampleloading ports 1214, openings 1248 to the thirteen reagent reservoirs1216, and opening 1250 to waste reservoir 1218. FIG. 40 also shows fourtreaded holes 1252 for receiving screws 1238. Further, FIG. 40 showsCMOS image sensor 262 and a portion of a protective cap 1254 that iscovering CMOS image sensor 262. Referring now to FIG. 41 , CMOS imagesensor 262 has been removed so that protective cap 1254 is fullyvisible. Referring now to FIG. 42 , protective cap 1254 has been removedshowing a clearance region 1256 in housing 1210 that is associated withCMOS image sensor 262.

FIG. 43 shows a transparent perspective view of housing 1210 ofmicrofluidic cartridge assembly 1200 in order to show the positions ofthe openings with respect to sample loading ports 1214, reagentreservoirs 1216, and waste reservoir 1218. Namely, in this view one cansee the positions of openings 1246 with respect to sample loading ports1214, the positions of openings 1248 with respect to reagent reservoirs1216, and the position of opening 1250 with respect to waste reservoir1218.

FIG. 44 shows a transparent perspective view of housing 1210 ofmicrofluidic cartridge assembly 1200 with the various fluidics channelsoverlaid thereon. Namely, in this view one can see the positions of thevarious fluidics channels with respect to sample loading ports 1214,reagent reservoirs 1216, and waste reservoir 1218. FIG. 45 shows across-sectional view of microfluidic cartridge assembly 1200 of FIG. 25, which shows more details thereof.

FIGS. 46A, 46B, 47A, 47B, and 48 show various views of housing 1210 ofmicrofluidic cartridge assembly 1200 of FIG. 25 , which shows moredetails thereof. Namely, FIGS. 46A and 46B show a plan view and a sideview, respectively, of housing 1210. In one example, housing 1210 isfrom about 12 mm to about 100 mm in height, from about 100 mm to about200 mm in length, from about 100 mm to about 200 mm in width. FIG. 47Ashows a perspective view of housing 1210 without foil seal 1220installed. FIG. 47B shows a perspective view of housing 1210 with foilseal 1220 installed. While FIGS. 46A, 46B, 47A, and 47B show the outsideof housing 1210, FIG. 48 shows a plan view of the inside of housing1210.

FIGS. 49, 50, 51A, 51B, and 52 show various views of base plate 1212 ofmicrofluidic cartridge assembly 1200 of FIG. 25 , which shows moredetails thereof. Namely, FIGS. 49 and 50 show perspective views of theoutside and inside, respectively, of base plate 1212. FIG. 41A shows aplan view of the outside of base plate 1212, while FIG. 41B shows a sideview of base plate 1212. FIGS. 49, 50, 51A, 38B, and 39 show that baseplate 1212 further includes four holes 1258 for receiving screws 1238, arecessed region 1260 with an opening 1262 at its center for receivinggrip portion 1240 and flow controller portion 1242 of rotatable valveassembly 1410.

FIGS. 53A and 53B illustrate other perspective views of fluidicsassembly 1400 of microfluidic cartridge assembly 1200 showing moredetails thereof. Namely, FIGS. 53A and 53B each show a perspective viewof fluidics assembly 1400. FIG. 53A shows fluidics assembly 1400 withoutflexible PCB heater 1412, whereas FIG. 53B shows fluidics assembly 1400with flexible PCB heater 1412 installed. Further, there is a notch 1414on one edge of fluidics layers 200 and within PCR region 270. Notch 1414is designed to receive flexible PCB heater 1412.

FIGS. 54A, 54B, and 54C illustrate various views showing more details offlexible PCB heater 1412 of fluidics assembly 1400 of microfluidiccartridge assembly 1200. Namely, FIGS. 54A and 54B show perspectiveviews of each side, respectively, of flexible PCB heater 1412, whileFIG. 54C shows a side view of flexible PCB heater 1412. Flexible PCBheater 1412 comprises a U-shaped wraparound panel 1416 and a sideextension panel 1418, all formed using flexible PCB technology. TheU-shaped wraparound panel 1416 comprises a panel 1420 and a panel 1422,each having a heater trace 1500 patterned therein, e.g., heater traces1500 a and 1500 b. An example of heater trace 1500 is shown in FIGS. 28Aand 28B. The space between panel 1420 and panel 1422 is set so thatflexible PCB heater 1412 can be press-fitted onto PCR region 270 offluidics layers 200 and fitted into notch 1414, as shown in FIG. 53B.FIGS. 54B and 41C also show I/O pads 1226, which provide the electricalconnections to the two heater traces 1500 as well as to CMOS imagesensor 262.

Side extension panel 1418 extends from panel 1420 near the bend in theU-shaped wraparound panel 1416. Side extension panel 1418 is designed toextend towards CMOS image sensor 262. As shown in FIG. 53B, the end ofside extension panel 1418 farthest from the U-shaped wraparound panel1416 is shaped to be fitted against CMOS image sensor 262. The purposeof side extension panel 1418 is to provide the electrical connection toCMOS image sensor 262, which is assembled atop the rigid or flexiblePCB.

FIGS. 55A and 55B show a perspective view and plan view, respectively,of inlet/outlet ports layer 210 of fluidics layers 200 shown in FIG. 15and FIG. 27 . Again, inlet/outlet ports layer 210 can be formed of, forexample, polycarbonate or any other materials that are suitable for usewith a R2R process. Inlet/outlet ports layer 210 provides the interfacebetween fluidics layers 200 and housing 1210 of microfluidic cartridgeassembly 1200. Namely, inlet/outlet ports layer 210 provides the fluidpaths from sample loading ports 1214, the thirteen reagent reservoirs1216, and waste reservoir 1218 of housing 1210 to fluidics channelslayer 220 of fluidics layers 200. For example, inlet/outlet ports layer210 includes a set of openings 212 that substantially align withopenings 1246 of sample loading ports 1214 in housing 1210. Inlet/outletports layer 210 includes a set of openings 214 that substantially alignwith openings 1248 of reagent reservoirs 1216 in housing 1210.Inlet/outlet ports layer 210 also includes an opening 216 thatsubstantially align with opening 1250 of waste reservoir 1218 in housing1210.

FIGS. 56A and 56B show a perspective view and plan view, respectively,of fluidics channels layer 220 of fluidics layers 200 shown in FIG. 15and FIG. 27 . Again, fluidics channels layer 220 can be formed of, forexample, polycarbonate or any other materials that are suitable for usewith a R2R process. Fluidics channels layer 220 is the layer of fluidicslayers 200 at which the flow of all liquids is facilitated. Namely, allPCR and sequencing operations take place at fluidics channels layer 220.PCR operations take place in PCR channels 222 at PCR region 270. PCRoutput channel 224 supplies reagent mixing and distribution region 275.Reagent distribution takes place using reagent channels 226 at reagentmixing and distribution region 275. The thirteen reagent channels 226are patterned to supply rotatable valve assembly 1410. Sequencing feedchannel 228 supplies the inlet of sequencing chamber 258 of sequencingchamber layer 250 shown in FIGS. 58A and 58B. Then, sequencing outletchannel 230 is fluidly connected to the outlet of sequencing chamber258.

FIGS. 57A and 57B show a perspective view and plan view, respectively,of flexible PCB layer 260 of fluidics layers 200 shown in FIG. 15 andFIG. 27 . Again, flexible PCB layer 260 can be formed of, for example,polyimide or any other materials that are suitable for use with a R2Rprocess. Flexible PCB layer 260 includes a set of openings (or holes)264 that correlate to the inlets/outlets of membrane valves 242.Flexible PCB layer 260 also includes a set of openings (or holes) 266that correlate to the inlets/outlets of membrane valves 244. If membranevalves 246 are present, flexible PCB layer 260 includes a set ofopenings (or holes) 267 that correlate to the inlets/outlets of membranevalves 246. Further, flexible PCB layer 260 includes a set of openings268 that substantially align with and provide fluid paths to rotatablevalve assembly 1410.

FIGS. 58A and 58B show a perspective view and plan view, respectively,of sequencing chamber bottom layer 280 of fluidics layers 200 shown inFIG. 15 and FIG. 27 . Again, sequencing chamber bottom layer 280 can beformed of, for example, polycarbonate or any other materials that aresuitable for use with a R2R process. Sequencing chamber bottom layer 280includes a set of openings 282 for forming membrane valves 242 withinthe stack of fluidics layers 200. Sequencing chamber bottom layer 280also includes a set of openings 284 for forming membrane valves 244within the stack of fluidics layers 200. If membrane valves 246 arepresent, sequencing chamber bottom layer 280 includes a set of openings286 for forming membrane valves 246 within the stack of fluidics layers200. Further, sequencing chamber bottom layer 280 includes a set ofopenings 288 that substantially align with and provide fluid paths torotatable valve assembly 1410. Additionally, sequencing chamber bottomlayer 280 includes a pair of openings 289, which fluidly couple tosequencing chamber 258 of sequencing chamber layer 250.

Sequencing chamber bottom layer 280 is the layer of fluidics layers 200at which the CMOS technology is integrated. Namely, CMOS image sensor262 is installed on sequencing chamber bottom layer 280. The position ofCMOS image sensor 262 substantially corresponds to the position ofsequencing chamber 258 of sequencing chamber layer 250.

FIGS. 59A and 59B show a perspective view and plan view, respectively,of sequencing chamber layer 250 of fluidics layers 200 shown in FIG. 15and FIG. 27 . Again, sequencing chamber layer 250 can be formed of, forexample, polycarbonate or any other materials that are suitable for usewith a R2R process. Sequencing chamber layer 250 is the layer offluidics layers 200 at which sequencing operations occur; namely, usingsequencing chamber 258.

Sequencing chamber layer 250 includes a set of openings 252 for formingmembrane valves 242 within the stack of fluidics layers 200. Sequencingchamber layer 250 also includes a set of openings 254 for formingmembrane valves 244 within the stack of fluidics layers 200. If membranevalves 246 are present, sequencing chamber layer 250 includes a set ofopenings 255 for forming membrane valves 246 within the stack offluidics layers 200. Further, sequencing chamber layer 250 includes aset of openings 256 that substantially align with and provide fluidpaths to rotatable valve assembly 1410.

FIGS. 60A and 60B show a perspective view and plan view, respectively,of membrane layer 240 and sequencing chamber top layer 290 of fluidicslayers 200 shown in FIG. 15 and FIG. 27 . Membrane layer 240 can beformed of, for example, silicone elastomer, while sequencing chamber toplayer 290 can be formed of, for example, COC. Membrane layer 240 servesas the elastic membrane for opening and closing membrane valves 242,244, and 246 within the stack of fluidics layers 200, wherein membranevalves 242, 244, and 246 are created by the combination of, in order,flexible PCB layer 260, sequencing chamber bottom layer 280, sequencingchamber layer 250, and membrane layer 240. FIGS. 60A and 60B also showssequencing chamber top layer 290, which is used to cover sequencingchamber 258 of sequencing chamber layer 250.

FIGS. 61A and 61B illustrate a flow diagram of an example of a method4800 of using microfluidic cartridge assembly 1200 to perform multiplexPCR and the downstream mixing needed for sequencing. Becausemicrofluidic cartridge assembly 1200 is based on microfluidic cartridge1100 shown in FIG. 24 , microfluidic cartridge assembly 1200 isconfigured for 4× sample multiplexing. Further, in method 4800 thethirteen reagent reservoirs 1216 are designated reagent reservoirs 1216a, 1216 b, 1216 c, 1216 d, 1216 e, 1216 f, 1216 g, 1216 h, 1216 i, 1216j, 1216 k, 1216 l, and 1216 m. Further, method 4800 utilizes outlet pump1114, which is fluidly connected to microfluidic cartridge assembly1200. Outlet pump 1114 is positioned downstream of sequencing chamber258. Outlet pump 1114 is capable of providing both positive pressure andnegative pressure (i.e., vacuum pressure). Method 4800 includes, but isnot limited to, the following steps.

At a step 4810, microfluidic cartridge assembly 1200 is provided thathas been prepared for use. Namely, microfluidic cartridge assembly 1200is provided with one or more of its reservoirs loaded with the desiredliquids. For example, reagent reservoirs 1216 can be filled with thesame or different reagent liquid. In one example, all of the reagentreservoirs 1216 a-m are filled with hydrogenation buffer (HT1). Method4800 proceeds to step 4815.

At a step 4815, all membrane valves are closed and then the samples/PCRMIX are loaded. “PCR MIX” means a PCR Master Mix that is optimized foruse in routine PCR for amplifying DNA templates. In this step, membranevalves 242 a and 244 a are closed, membrane valves 242 b and 244 b areclosed, membrane valves 242 c and 244 c are closed, and membrane valves242 d and 244 d are closed. In this way, PCR channels 222 a, 222 b, 222c, and 222 d are all completely sealed off. Then, a first sample liquidis mixed with a PCR MIX (hereafter called sample/PCR_MIX1) and loadedinto sample loading port 1214 a. A second sample liquid is mixed with aPCR MIX (hereafter called sample/PCR_MIX2) and loaded into sampleloading port 1214 b. A third sample liquid is mixed with a PCR MIX(hereafter called sample/PCR_MIX3) and loaded into sample loading port1214 c. A fourth sample liquid is mixed with a PCR MIX (hereafter calledsample/PCR_MIX4) and loaded into sample loading port 1214 d. At thecompletion of this step, a volume of sample/PCR MIX is sitting in eachof the sample loading ports 1214 and ready for processing. Method 4800proceeds to step 4820.

At a step 4820, the membrane valves for the first sample are opened.Then, the first sample is pulled into the PCR region. Then, the membranevalves for the first sample are closed. For example, membrane valves 242a and 244 a for PCR channel 222 a are opened. Then, using outlet pump1114, sample/PCR_MIX1 is pulled into PCR channel 222 a. Then, membranevalves 242 a and 244 a for PCR channel 222 a are closed, wherein avolume of sample/PCR_MIX1 is now sealed inside of PCR channel 222 a.Method 4800 proceeds to step 4825.

At a decision step 4825, it is determined whether another sample awaitsto be loaded into the PCR region, i.e., into PCR region 270. If yes,then method 4800 proceeds to step 4830. If no, then method 4800 proceedsto step 4835.

At a step 4830, the membrane valves for the next sample are opened.Then, the next sample is pulled into the PCR region. Then, the membranevalves for the next sample are closed. In one example, membrane valves242 b and 244 b for PCR channel 222 b are opened. Then, using outletpump 1114, sample/PCR_MIX2 is pulled into PCR channel 222 b. Then,membrane valves 242 b and 244 b for PCR channel 222 b are closed,wherein a volume of sample/PCR_MIX2 is now sealed inside of PCR channel222 b.

In another example, membrane valves 242 c and 244 c for PCR channel 222c are opened. Then, using outlet pump 1114, sample/PCR_MIX3 is pulledinto PCR channel 222 c. Then, membrane valves 242 c and 244 c for PCRchannel 222 c are closed, wherein a volume of sample/PCR_MIX3 is nowsealed inside of PCR channel 222 c.

In yet another example, membrane valves 242 d and 244 d for PCR channel222 d are opened. Then, using outlet pump 1114, sample/PCR_MIX4 ispulled into PCR channel 222 d. Then, membrane valves 242 d and 244 d forPCR channel 222 d are closed, wherein a volume of sample/PCR_MIX4 is nowsealed inside of PCR channel 222 d.

Method 4800 returns to step 4825.

At a step 4835, with sample/PCR_MIX1 in PCR channel 222 a,sample/PCR_MIX2 in PCR channel 222 b, sample/PCR_MIX3 in PCR channel 222c, and sample/PCR_MIX4 in PCR channel 222 d, PCR operations areperformed. Upon completion of the PCR operations, sample/PCR_MIX1 is nowreferred to as PCR_MIX1, sample/PCR_MIX2 is now referred to as PCR_MIX2,sample/PCR_MIX3 is now referred to as PCR_MIX3, and sample/PCR_MIX4 isnow referred to as PCR_MIX4. Method 4800 proceeds to step 4840.

At a step 4840, the rotatable valve is rotated to the first PRC MIXposition. For example, by rotating grip portion 1240 of rotatable valveassembly 1410, the position of rotatable valve assembly 1410 is set toPCR channel 222 a, which is holding PCR_MIX1. Method 4800 proceeds tostep 4845.

At a step 4845, the membrane valves for the first PCR MIX are opened.Then, the first PCR MIX is pulled through the rotatable valve toward theCMOS device. Then, the membrane valves for the first PCR MIX are closed.For example, membrane valves 242 a and 244 a for PCR channel 222 a areopened. Then, using outlet pump 1114, PCR_MIX1 is pulled out of PCRchannel 222 a, into PCR output channel 224, and through rotatable valveassembly 1410. Then, membrane valves 242 a and 244 a are closed. Method4800 proceeds to step 4850.

At a step 4850, the rotatable valve is rotated to the hydrogenationbuffer (HT1) position, meaning to the reagent reservoir 1216 that isholding HT1. In method 4800, at least one reagent reservoir 1216 isholding a volume of HT1. By way of example, reagent reservoir 1216 k isholding the volume of HT1. Therefore, by rotating grip portion 1240 ofrotatable valve assembly 1410, the position of rotatable valve assembly1410 is now set to reagent reservoir 1216 k, which is holding the HT1.Method 4800 proceeds to step 4855.

At a step 4855, the first PCR MIX is pushed into the HT1 reservoir. Forexample, using outlet pump 1114, PCR_MIX1 is pushed through rotatablevalve assembly 1410 and into reagent reservoir 1216 k and mixed with theHT1 therein. Method 4800 proceeds to step 4860.

At a decision step 4860, it is determined whether another PCR MIX awaitsto be mixed with the HT1. If yes, then method 4800 proceeds to step4865. If no, then method 4800 proceeds to step 4885.

At a step 4865, the rotatable valve is rotated to the next PRC MIXposition. In one example, by rotating grip portion 1240 of rotatablevalve assembly 1410, the position of rotatable valve assembly 1410 isset to PCR channel 222 b, which is holding PCR_MIX2. In another example,by rotating grip portion 1240 of rotatable valve assembly 1410, theposition of rotatable valve assembly 1410 is set to PCR channel 222 c,which is holding PCR_MIX3. In yet another example, by rotating gripportion 1240 of rotatable valve assembly 1410, the position of rotatablevalve assembly 1410 is set to PCR channel 222 d, which is holdingPCR_MIX4. Method 4800 proceeds to step 4870.

At a step 4870, the membrane valves for the next PCR MIX are opened.Then, the next PCR MIX is pulled through the rotatable valve toward theCMOS device. Then, the membrane valves for the next PCR MIX are closed.In one example, membrane valves 242 b and 244 b for PCR channel 222 bare opened. Then, using outlet pump 1114, PCR_MIX2 is pulled out of PCRchannel 222 b, into PCR output channel 224, and through rotatable valveassembly 1410. Then, membrane valves 242 b and 244 b are closed. Inanother example, membrane valves 242 c and 244 c for PCR channel 222 care opened. Then, using outlet pump 1114, PCR_MIX3 is pulled out of PCRchannel 222 c, into PCR output channel 224, and through rotatable valveassembly 1410. Then, membrane valves 242 c and 244 c are closed. In yetanother example, membrane valves 242 d and 244 d for PCR channel 222 dare opened. Then, using outlet pump 1114, PCR_MIX4 is pulled out of PCRchannel 222 d, into PCR output channel 224, and through rotatable valveassembly 1410. Then, membrane valves 242 d and 244 d are closed. Method4800 proceeds to step 4875.

At a step 4875, the rotatable valve is rotated to the HT1 position. Forexample, by rotating grip portion 1240 of rotatable valve assembly 1410,the position of rotatable valve assembly 1410 is returned to reagentreservoir 1216 k, which is holding the HT1. Method 4800 proceeds to step4880.

At a step 4880, the next PCR MIX is pushed into the HT1 reservoir. Inone example, using outlet pump 1114, PCR_MIX2 is pushed throughrotatable valve assembly 1410 and into reagent reservoir 1216 k andmixed with the HT1 therein. In another example, using outlet pump 1114,PCR_MIX3 is pushed through rotatable valve assembly 1410 and intoreagent reservoir 1216 k and mixed with the HT1 therein. In yet anotherexample, using outlet pump 1114, PCR_MIX4 is pushed through rotatablevalve assembly 1410 and into reagent reservoir 1216 k and mixed with theHT1 therein. Method 4800 returns to step 4860.

At a step 4885, the mixture from the HT1 reservoir is pulled into thesequencing chamber and the clustering/sequencing recipe is executed. Forexample, with reagent reservoir 1216 k now holding a mixture of the HT1,PCR_MIX1, PCR_MIX2, PCR_MIX3, and PCR_MIX4, this mixture is pulled outof reagent reservoir 1216 k, then pulled along sequencing feed channel228 and into sequencing chamber 258. Then, using CMOS image sensor 262,the clustering/sequencing recipe is executed. Method 4800 ends.

One or more embodiments may include CMOS Flow Cell having an accessiblebiosensor active area. For instance, a CMOS flow cell may be designed asa single use consumable item. Accordingly, it may be beneficial for theCMOS flow cell to be a small and inexpensive device. In a small CMOSflow cell it is important to use as much of the biosensor active area aspossible. However, current CMOS flow cell designs do not allow for 100percent utilization of the biosensor active area. Therefore, newapproaches are needed to provide increased utilization of the biosensoractive area in a CMOS flow cell. Embodiments set forth herein mayinclude a CMOS flow cell, wherein most or up to about 100% of thebiosensor active area is accessible for reagent delivery andillumination, as shown and described herein below with reference toFIGS. 62 through 75 .

FIG. 62 illustrates a side view of an example of a CMOS flow cell 4900,wherein most or up to about 100% of the biosensor active area isaccessible for reagent delivery and illumination. CMOS flow cell 4900includes a PCB substrate 4910, which is, for example, a flexible PCBsubstrate. Atop PCB substrate 4910 is a CMOS biosensor device 4920. CMOSbiosensor device 4920 is a CMOS image sensor with a biolayer thereon.Also atop PCB substrate 4910 and surrounding CMOS biosensor device 4920is a laminate film 4930. Laminate film 4930 can be formed, for example,of epoxy, polyimide or other plastic film, silicon, Kapton®,Bismaleimide-Triazine (BT) substrates, and the like. PCB substrate 4910and laminate film 4930 can be formed using flexible PCB technology. Aplanarization surface can also be created by machining a cavity in thePCB substrate

The purpose of laminate film 4930 is to provide an extended surfacearound the perimeter of CMOS biosensor device 4920 that is substantiallyplanar with the top of CMOS biosensor device 4920. In one example, ifthe die thickness of CMOS biosensor device 4920 is about 100 μm, thenthe thickness of laminate film 4930 is about 100 μm±about 5 μm.

A slight gap between PCB substrate 4910 and laminate film 4930 forms atrench or channel 4950 around the perimeter of CMOS biosensor device4920. The width of trench or channel 4950 can be, for example, fromabout 100 μm to about 1000 μm. Trench or channel 4950 is filled withfiller material 4952 in order to form a substantially continuous planarsurface across both CMOS biosensor device 4920 and laminate film 4930.Filler material 4952 is a material that does not interfere with thereactions that take place atop CMOS biosensor device 4920. Fillermaterial 4952 can be, for example, ultraviolet (UV)-cured epoxy,thermal-cured epoxy, or the like.

Atop CMOS biosensor device 4920 and laminate film 4930 is a flow celllid 4940 in which a flow channel 4942 is integrated. Further, flow celllid 4940 includes a first port 4944 and a second port 4946 that provideinlet/outlet ports to flow channel 4942. Flow cell lid 4940 is formed ofa material that is optically transparent and has low or noautoflourescence in the part of the spectrum that will be used foranalytical detection, such as, but not limited to, cyclic olefincopolymer (COC). The overall thickness of flow cell lid 4940 can be, forexample, from about 300 μm to about 1000 μm. A bond area exists outsideof flow channel 4942 for bonding flow cell lid 4940 to laminate film4930. Bonding can be via a low autoflourescence adhesive.

Because a substantially continuous planar surface exists across bothCMOS biosensor device 4920 and laminate film 4930, the area of flowchannel 4942 within flow cell lid 4940 can be sized to span across thefull CMOS biosensor device 4920; namely, it can span about 100% of thebiosensor active area. In one example, if the die size of CMOS biosensordevice 4920 is about 8 mm×9 mm, then the active area is about 7 mm×8 mm.However, the die size of CMOS biosensor device 4920 can range, forexample, up to about 25 mm×25 mm, with a proportionately larger activearea.

FIG. 62 shows, for example, a reagent fluid 4954 filling flow channel4942. Chemical reactions take place in reagent fluid 4954 in flowchannel 4942, which is atop CMOS biosensor device 4920. When illuminatedthrough flow cell lid 4940, CMOS biosensor device 4920 is used to sensethe chemical reactions that take place in flow channel 4942. Electricalconnections (not shown) are provided through PCB substrate 4910 foracquiring the signals from CMOS biosensor device 4920. In CMOS flow cell4900, about 100% of the biosensor active area of CMOS biosensor device4920 is accessible for reagent delivery and illumination.

FIG. 63 illustrates an exploded view of an example of one instantiationof CMOS flow cell 4900 shown in FIG. 62 . FIG. 63 shows that CMOSbiosensor device 4920 includes an active area 4922. Any portion of CMOSbiosensor device 4920 outside of active area 4922 is inactive area 4924.CMOS biosensor device 4920 can be attached to PCB substrate 4910 using,for example, flip-chip technology. Further, laminate film 4930 includesan opening or window 4932 that is sized for receiving CMOS biosensordevice 4920 when laminated against PCB substrate 4910. Opening or window4932 is provided in laminate film 4930 in advance of laminating laminatefilm 4930 to PCB substrate 4910. When flow cell lid 4940 is bonded tolaminate film 4930, flow channel 4942 substantially aligns with CMOSbiosensor device 4920 and its area extends beyond the area of CMOSbiosensor device 4920. In FIG. 63 , flow cell lid 4940 is shown astransparent. FIGS. 64 and 65 illustrate a perspective view and a sideview, respectively, of CMOS flow cell 4900 shown in FIG. 63 when fullyassembled.

FIG. 66 illustrates perspective views of an example of flow cell lid4940 of CMOS flow cell 4900 shown in FIGS. 63, 64, and 65 . Namely, FIG.66 shows a top and bottom perspective view of flow cell lid 4940 of CMOSflow cell 4900 shown in FIGS. 63, 64, and 65 . In this example, thediameter of first port 4944 and second port 4946 can be about 750 μm.Further, the depth or height of flow channel 4942 can be about 100 μm.

FIGS. 67, 68, 69, and 70 illustrate an example of a process of providingan extended planar surface in a CMOS flow cell, upon which a flow celllid may be mounted.

In a first step and referring now to FIG. 67 , laminate film 4930 andCMOS biosensor device 4920 are provide atop PCB substrate 4910. Trenchor channel 4950 exists around the perimeter of CMOS biosensor device4920. Trench or channel 4950 exists because opening or window 4932 inlaminate film 4930 is slightly larger than CMOS biosensor device 4920.

In a next step and referring now to FIG. 68 , the upper side of trenchor channel 4950 is sealed with, for example, an optically transparentelastomer 4960 that has features for fitting tightly against trench orchannel 4950. Elastomer 4960 is optically transparent so that UV lightcan pass therethrough. The purpose of elastomer 4960 is to block the topof trench or channel 4950 in preparation for filling.

In a next step and referring now to FIG. 69 , using, for example, a pairof through-holes 4916 in PCB substrate 4910, trench or channel 4950 isfilled with filler material 4952, such as UV-cured epoxy, which is thereason that elastomer 4960 is optically transparent.

In a next step and referring now to FIG. 70 , once filler material 4952is cured, elastomer 4960 is removed and a substantially continuousplaner surface is now present in the flow cell for receiving a flow celllid, such as flow cell lid 4940.

FIGS. 71A, 71B, 71C, and 71D illustrate another example of a process ofproviding an extended planar surface in a CMOS flow cell, upon which aflow cell lid may be mounted.

In a first step and referring now to FIG. 71A, CMOS biosensor device4920 is provided atop PCB substrate 4910.

In a next step and referring now to FIG. 71B, a mold 5510 (e.g., aclamshell type mold) is provided around CMOS biosensor device 4920 andPCB substrate 4910. Mold 5510 provides a space or void 5512 atop PCBsubstrate 4910 and around the perimeter of CMOS biosensor device 4920.

In a next step and referring now to FIG. 71C, using, for example, a lowpressure injection molding process or a reaction injection moldingprocess, space or void 5512 in mold 5510 is filled with filler material4952, such as UV-cured or thermal-cured epoxy.

In a next step and referring now to FIG. 71D, once filler material 4952is cured, mold 5510 is removed and a substantially continuous planersurface is now present in the flow cell for receiving a flow cell lid,such as flow cell lid 4940.

FIGS. 72, 73, 74, and 75 illustrate yet another example of a process ofproviding an extended planar surface in a CMOS flow cell, upon which aflow cell lid may be mounted.

In a first step and referring now to FIG. 72 , CMOS biosensor device4920 is provided atop PCB substrate 4910. Also, a mechanical materialpiece 5910 is provided atop PCB substrate 4910 and at one end of CMOSbiosensor device 4920. Similarly, a mechanical material piece 5912 isprovided atop PCB substrate 4910 and at the other end of CMOS biosensordevice 4920. Mechanical material pieces 5910 and 5912 can be, forexample, blank silicon, glass, or plastic. A trench or channel 5914 isbetween mechanical material piece 5910 and CMOS biosensor device 4920.Another trench or channel 5914 is between mechanical material piece 5912and CMOS biosensor device 4920.

In a next step and referring now to FIG. 73 , a set of barriers 5916 areprovided at the ends of trenches or channels 5914. For example, barriers5916 a and 5916 b are blocking the ends of one trench or channel 5914and barriers 5916 c and 5916 d are blocking the ends of the other trenchor channel 5914 in preparation for filling.

In a next step and referring now to FIG. 74 , trenches or channels 5914are filled with filler material 4952, such as UV-cured or thermal-curedepoxy. Filler material 4952 is retained between barriers 5916 a and 5916b and between barriers 5916 c and 5916 d.

In a next step and referring now to FIG. 75 , once filler material 4952is cured, a substantially continuous planer surface is now present inthe flow cell for receiving a flow cell lid, such as flow cell lid 4940.

It will be appreciated that various aspects of the present disclosuremay be embodied as a method, system, computer readable medium, and/orcomputer program product. Aspects of the present disclosure may take theform of hardware embodiments, software embodiments (including firmware,resident software, micro-code, etc.), or embodiments combining softwareand hardware aspects that may all generally be referred to herein as a“circuit,” “module,” or “system.” Furthermore, the methods of thepresent disclosure may take the form of a computer program product on acomputer-usable storage medium having computer-usable program codeembodied in the medium.

Any suitable computer useable medium may be utilized for softwareaspects of the present disclosure. The computer-usable orcomputer-readable medium may be, for example but not limited to, anelectronic, magnetic, optical, electromagnetic, infrared, orsemiconductor system, apparatus, device, or propagation medium. Thecomputer readable medium may include transitory and/or non-transitoryembodiments. More specific examples (a non-exhaustive list) of thecomputer-readable medium would include some or all of the following: anelectrical connection having one or more wires, a portable computerdiskette, a hard disk, a random access memory (RAM), a read-only memory(ROM), an erasable programmable read-only memory (EPROM or Flashmemory), an optical fiber, a portable compact disc read-only memory(CD-ROM), an optical storage device, a transmission medium such as thosesupporting the Internet or an intranet, or a magnetic storage device.Note that the computer-usable or computer-readable medium could even bepaper or another suitable medium upon which the program is printed, asthe program can be electronically captured, via, for instance, opticalscanning of the paper or other medium, then compiled, interpreted, orotherwise processed in a suitable manner, if necessary, and then storedin a computer memory. In the context of this document, a computer-usableor computer-readable medium may be any medium that can contain, store,communicate, propagate, or transport the program for use by or inconnection with the instruction execution system, apparatus, or device.

Program code for carrying out operations of the methods and apparatusset forth herein may be written in an object oriented programminglanguage such as Java, Smalltalk, C++ or the like. However, the programcode for carrying out operations of the methods and apparatus set forthherein may also be written in conventional procedural programminglanguages, such as the “C” programming language or similar programminglanguages. The program code may be executed by a processor, applicationspecific integrated circuit (ASIC), or other component that executes theprogram code. The program code may be simply referred to as a softwareapplication that is stored in memory (such as the computer readablemedium discussed above). The program code may cause the processor (orany processor-controlled device) to produce a graphical user interface(“GUI”). The graphical user interface may be visually produced on adisplay device, yet the graphical user interface may also have audiblefeatures. The program code, however, may operate in anyprocessor-controlled device, such as a computer, server, personaldigital assistant, phone, television, or any processor-controlled deviceutilizing the processor and/or a digital signal processor.

The program code may locally and/or remotely execute. The program code,for example, may be entirely or partially stored in local memory of theprocessor-controlled device. The program code, however, may also be atleast partially remotely stored, accessed, and downloaded to theprocessor-controlled device. A user's computer, for example, mayentirely execute the program code or only partly execute the programcode. The program code may be a stand-alone software package that is atleast partly on the user's computer and/or partly executed on a remotecomputer or entirely on a remote computer or server. In the latterscenario, the remote computer may be connected to the user's computerthrough a communications network.

The methods and apparatus set forth herein may be applied regardless ofnetworking environment. The communications network may be a cablenetwork operating in the radio-frequency domain and/or the InternetProtocol (IP) domain. The communications network, however, may alsoinclude a distributed computing network, such as the Internet (sometimesalternatively known as the “World Wide Web”), an intranet, a local-areanetwork (LAN), and/or a wide-area network (WAN). The communicationsnetwork may include coaxial cables, copper wires, fiber optic lines,and/or hybrid-coaxial lines. The communications network may even includewireless portions utilizing any portion of the electromagnetic spectrumand any signaling standard (such as the IEEE 802 family of standards,GSM/CDMA/TDMA or any cellular standard, and/or the ISM band). Thecommunications network may even include powerline portions, in whichsignals are communicated via electrical wiring. The methods andapparatus set forth herein may be applied to any wireless/wirelinecommunications network, regardless of physical componentry, physicalconfiguration, or communications standard(s).

Certain aspects of present disclosure are described with reference tovarious methods and method steps. It will be understood that each methodstep can be implemented by the program code and/or by machineinstructions. The program code and/or the machine instructions maycreate means for implementing the functions/acts specified in themethods.

The program code may also be stored in a computer-readable memory thatcan direct the processor, computer, or other programmable dataprocessing apparatus to function in a particular manner, such that theprogram code stored in the computer-readable memory produce or transforman article of manufacture including instruction means which implementvarious aspects of the method steps.

The program code may also be loaded onto a computer or otherprogrammable data processing apparatus to cause a series of operationalsteps to be performed to produce a processor/computer implementedprocess such that the program code provides steps for implementingvarious functions/acts specified in the methods of the presentdisclosure.

In an embodiment, a system is provided that includes a removablecartridge having a cartridge housing. The removable cartridge alsoincludes a fluidic network that is disposed within the cartridgehousing. The fluidic network is configured to receive and fluidicallydirect a biological sample to conduct at least one of sample analysis orsample preparation. The removable cartridge also includes a flow-controlvalve that is operably coupled to the fluidic network and is movablerelative to the fluidic network to control flow of the biological sampletherethrough. The cartridge housing includes a housing side that definesan exterior of the removable cartridge and permits operative access tothe flow-control valve. The system also includes a base instrumenthaving a control side that is configured to separably engage the housingside of the removable cartridge. The housing and control sidescollectively define a system interface. The base instrument includes avalve actuator that engages the flow-control valve through the systeminterface. The removable cartridge also includes a detection assemblythat is held by at least one of the removable cartridge or the baseinstrument. The detection assembly includes an imaging detector and areaction chamber that is in flow communication with the fluidic network.The imaging detector is configured to detect designated reactions withinthe reaction chamber.

In one aspect, the control side of a base instrument set forth hereinand the housing side of a removable cartridge set forth herein aregenerally planar and face each other. The system interface may be asingle-sided interface in which the base instrument and the removablecartridge are operably coupled to each other only through the housingside and the control side. Optionally, the base instrument and theremovable cartridge may be operably coupled such that the baseinstrument and the removable cartridge are secured to each other at thesystem interface with at least one of a fluidic coupling, an electriccoupling, or a thermal coupling established through the systeminterface.

In another aspect, the control side of a base instrument set forthherein may represent a top of the base instrument, with respect togravity, such that the removable cartridge sits on and is supported bythe base instrument.

In another aspect, the valve actuator of a base instrument set forthherein may include an elongated actuator body that extends through thehousing side and into the cartridge housing.

In another aspect, the flow-control valve of a removable cartridge setforth herein may include an elongated actuator body that extends throughthe control side and into the base instrument.

In another aspect, a base instrument set forth herein may have aninstrument side that faces in an opposite direction with respect to thecontrol side. The base instrument may have an instrument dimension thatextends between the control side and the instrument side. The baseinstrument and the removable cartridge may have a combined dimensionthat is greater than the instrument dimension.

In another aspect, each of a removable cartridge and a base instrumentmay include a contact array of electrical contacts. The contact arraysmay be electrically coupled to one another at the system interface.

In another aspect, the housing side of a removable cartridge set forthherein may be a first housing side and the cartridge housing may alsoinclude a second housing side. The first and second housing sides facein different directions. The system interface is a multi-sided interfacein which the base instrument and the removable cartridge are operablycoupled to each other along each of the first and second housing sides.

Optionally, the first and second housing sides of a removable cartridgeset forth herein may be generally perpendicular to each other. The baseinstrument may have an instrument housing that includes first and secondcontrol sides that face in perpendicular directions and form anopen-sided recess of the base instrument. At least a portion of theremovable cartridge may be disposed within the open-sided recess suchthat the first and second housing sides engage the first and secondcontrol sides.

In one aspect, the valve actuator of a base instrument set forth hereinmay include an elongated body that extends through the system interfacebetween the first housing side and the first control side. The secondhousing side and the second control side may include respective contactarrays of electrical contacts. The contact arrays may be electricallycoupled to each other along the system interface.

In another aspect, the first and second housing sides of a removablecartridge set forth herein face in generally opposite directions. Thebase instrument may have an instrument side and a cartridge-receivingslot that opens to the instrument side. The removable cartridge may bedisposed within the cartridge-receiving slot.

In another aspect, the removable cartridge and the base instrument arefluidically coupled along the first housing side and electricallycoupled along the second housing side. Optionally, the base instrumentincludes a locking mechanism that engages at least one of the firsthousing side or the second housing side to hold the removable cartridgewithin the base instrument.

In another aspect, each of the removable cartridge and the baseinstrument may include a flow port. The flow ports fluidically couple toeach other at the system interface.

In another aspect, a system set forth herein may include a lockingmechanism that is attached to at least one of the removable cartridge orthe base instrument. The locking mechanism is configured to removablysecure the cartridge housing to the base instrument.

In another aspect, an imaging detector of a system set forth herein maybe held by the base instrument and the reaction chamber may be held bythe removable cartridge.

In another aspect, the flow-control valve of a removable cartridge setforth herein may include a flexible membrane that is configured tocontrol the flow of the biological sample through the fluidic network.The flexible membrane may be flexed between first and second conditionsby the valve actuator.

In another aspect, the housing side of the cartridge housing of aremovable cartridge set forth herein may include an access openingtherethrough that receives the valve actuator.

In another aspect, the flow-control valve of a base instrument set forthherein may include a rotatable valve that is configured to control theflow of the fluid through the fluidic network. The rotatable valve maybe rotated by the valve actuator.

In another aspect, a base instrument set forth herein may include athermal block and the fluidic network of the cartridge housing mayinclude a sample channel where designated reactions with the biologicalsample occur. The housing side may include an access opening thatextends along the sample channel and is configured to receive thethermal block for changing a temperature of the sample channel.

In another aspect, the fluidic network of a removable cartridge setforth herein may include a plurality of channels and a storage module.The storage module may include a plurality of reservoirs for storingreagents that are used for at least one of sample preparation or sampleanalysis.

In another aspect, a base instrument set forth herein includes a systemcontroller having a valve-control module configured to control operationof the valve actuator to control flow of the biological sample throughthe fluidic network.

In an embodiment, a method of sequencing nucleic acids is provided. Themethod includes providing a removable cartridge having a cartridgehousing, a fluidic network disposed within the cartridge housing, and aflow-control valve that is operably coupled to the fluidic network andmovable relative to the fluidic network. The cartridge housing includesa housing side that defines an exterior of the removable cartridge. Themethod also includes contacting the removable cartridge to a baseinstrument. The housing side of the removable cartridge separablyengages a control side of the base instrument to collectively define asystem interface. The base instrument includes a valve actuator thatengages the flow-control valve through the system interface. The methodalso includes fluidically directing a biological sample to flow throughthe fluidic network of the cartridge to conduct at least one of sampleanalysis or sample preparation in the cartridge. The biological sampleis directed to flow into a reaction chamber, wherein the flow of thebiological sample is controlled by action of the valve actuator on theflow-control valve. The method also includes detecting the biologicalsample using an imaging detector directed to the reaction chamber,wherein the detection assembly is held by at least one of the removablecartridge or the base instrument.

In one aspect, a method set forth herein may also include removing theremovable cartridge from the base instrument. The removable cartridgecan be replaced by functionally mating a second removable cartridge withthe base instrument. Several removable cartridges can be sequentiallymated with the base instrument, used to prepare and/or analyze a samplewhile mated with the base instrument and then removed from the baseinstrument.

Accordingly, the method may include contacting a second removablecartridge with the base instrument, wherein the housing side of thesecond removable cartridge separably engages the control side of thebase instrument to collectively define the system interface.

In another aspect, a method set forth herein includes removing theremovable cartridge from the base instrument. Optionally, the methodincludes contacting a second removable cartridge with the baseinstrument, wherein the housing side of the second removable cartridgeseparably engages the control side of the base instrument tocollectively define the system interface.

In another aspect of a method set forth herein, fluidically directing abiological sample and imaging the biological sample are repeatedmultiple times in sequence in a single removable cartridge.

In another aspect, a method set forth herein includes sealing thebiological sample within a sample-preparation region of the fluidicnetwork and amplifying the biological sample while the biological sampleis sealed within the sample-preparation region.

In another aspect, the flow-control valve used in a method set forthherein includes a movable valve having at least one flow channel thatextends between valve ports, the valve actuator configured to move themovable between different positions.

In another aspect, the movable valve used in a method set forth hereinis in a sample position when the biological sample flows through theflow channel and is directed into the reaction chamber, the methodfurther comprising moving the movable valve to a component position andflowing a reagent through the flow channel into the reaction chamber,the reagent reacting with the biological sample in the reaction chamber.

In another aspect of a method set forth herein, the component positionincludes a plurality of component positions, the method furthercomprising moving the movable valve between the component positions inaccordance with a predetermined sequence to flow different reagents intothe reaction chamber.

In another aspect, the biological sample used in a method set forthherein includes nucleic acids and the predetermined sequence is inaccordance with a sequencing-by-synthesis (SBS) protocol.

In another aspect, a flow cell used in a method set forth hereinincludes the reaction chamber. The biological sample is immobilized toone or more surfaces of the flow cell.

In an embodiment, a removable cartridge is provided that includes acartridge housing having a sample port that opens to an exterior of thecartridge housing and is configured to receive a biological sample. Thecartridge housing has an array of electrical contacts and a mechanicalinterface that are exposed to the exterior. The cartridge housing isconfigured to be removably coupled to a base instrument. The removablecartridge may also include a fluidic network having a plurality ofchannels, a reaction chamber, and a storage module. The storage moduleincludes a plurality of reservoirs for storing reagents. The fluidicnetwork is configured to direct reagents from the reservoirs to thereaction chamber, wherein the mechanical interface is movable relativeto the fluidic network to control flow of fluid through the fluidicnetwork. The system also includes an imaging device disposed within thecartridge housing and positioned to detect designated reactions withinthe reaction chamber. The imaging device is electrically coupled to thearray of electrical contacts for communicating with the base instrument.The mechanical interface may be configured to be moved by a baseinstrument when the removable cartridge is coupled to the baseinstrument.

In one aspect, the mechanical interface of a removable cartridge setforth herein may include a channel valve that is configured to controlthe flow of the fluid through one of the channels of the fluidicnetwork.

In another aspect, the cartridge housing of a removable cartridge setforth herein may include an access opening that permits access to themechanical interface. Optionally, the mechanical interface includes arotatable valve.

In another aspect, the cartridge housing of a removable cartridge setforth herein may include an access opening that is exposed to theexterior, and the channels include a sample channel that is in flowcommunication with the sample port. The access opening may extend alongthe sample channel and may be configured to receive a thermal block forcontrolling a temperature of the sample channel.

In another aspect, the cartridge housing of a removable cartridge setforth herein may include a fluidic-coupling port that is exposed to theexterior and is in flow communication with the fluidic network. Thefluidic-coupling port is configured to engage an instrument port toreceive fluid therethrough.

In another aspect, the cartridge housing of a removable cartridge setforth herein may include first and second housing sides that face inopposite directions. The first housing side may include the array ofelectrical contacts. The second housing side may include the mechanicalinterface.

In another aspect, the removable cartridge also includes a lockingmechanism that may be attached to the cartridge housing. The lockingmechanism may be configured to removably secure the cartridge housing tothe base instrument.

In an embodiment, a removable cartridge is provided that includes acartridge housing having a sample port that opens to an exterior of thecartridge housing and is configured to receive a biological sample. Theremovable cartridge may also include a rotatable valve that is disposedwithin the cartridge housing. The rotatable valve has a fluidic side anda plurality of valve ports that open at the fluidic side. The rotatablevalve has at least one flow channel extending between the valve ports,wherein the rotatable valve is rotatable between different rotationalpositions. The removable cartridge may also include a microfluidic bodyhaving a body side that is slidably coupled to the fluidic side of therotatable valve. The microfluidic body may at least partially define afluidic network that includes a sample channel in flow communicationwith the sample port. The sample channel has a network port that opensto the body side of the microfluidic body. The fluidic network may alsoinclude a reservoir configured to hold a reagent. The reservoir is inflow communication with a reservoir port that opens to the fluidic sideof the microfluidic body. The fluidic network also includes a feedchannel in flow communication with a reaction chamber of the fluidicnetwork. The feed channel has a feed port that opens to the body side ofthe microfluidic body. The rotatable valve is configured to rotatebetween first and second rotational positions. The network port isfluidically coupled to the feed port through the rotatable valve whenthe rotatable valve is in the first rotational position. The reservoirport is fluidically coupled to the feed port through the rotatable valvewhen the rotatable valve is in the second rotational position.

In one aspect, the cartridge housing of a removable cartridge set forthherein may have an exterior side that is configured to engage a baseinstrument. The rotatable valve may include a mechanical interface thatis accessible at the exterior side and is configured to engage the baseinstrument.

In another aspect, the rotatable valve in the first rotational positionmay be configured, in a removable cartridge set forth herein, to receivea sample liquid when a suction force draws the sample liquid toward thefeed port. The rotatable valve in the second rotational position may beconfigured to allow the sample liquid to be displaced into the reservoirwhen a displacement force pushes the sample liquid away from the feedport into the reservoir.

In another aspect, the rotatable valve of a removable cartridge setforth herein rotates about an axis. The feed port may be aligned withthe axis.

In an embodiment, a removable cartridge is provided that includes acartridge housing having a sample port that opens to an exterior of thecartridge housing and is configured to receive a biological sample. Thecartridge housing may include a mating side that is configured to faceand removably couple to a base instrument. The removable cartridge alsoincludes a fluidic network that is disposed within the housing. Thefluidic network includes a sample channel that is in flow communicationwith the sample port. The removable cartridge also includes a channelvalve having a flex member that is configured to move between first andsecond positions. The flex member blocks flow through the sample channelwhen in the first position and permits flow through the sample channelwhen in the second position. The mating side of the cartridge housingincludes an access opening that exposes the channel valve to theexterior of the cartridge housing. The access opening is configured toreceive an actuator of the base instrument for moving the flex memberbetween the first and second positions.

In another aspect, the flex member of a removable cartridge set forthherein may include a flexible layer that covers an interior cavity ofthe fluidic network. The flexible layer may be configured to be pushedinto the cavity to block flow therethrough.

In another aspect, the removable cartridge also includes a rotatablevalve that is disposed within the cartridge housing. The rotatable valveis configured to rotate between different positions to change a flowpath of the fluidic network. The rotatable valve may include amechanical interface that is accessible along the mating side.

In another aspect, the fluidic network of a removable cartridge setforth herein may include a network port in flow communication with thesample channel, a feed port in flow communication with a reactionchamber, and a reservoir port in flow communication with a reservoirthat is configured to store a reagent. The removable cartridge may alsoinclude a rotatable valve disposed within the cartridge housing. Therotatable valve may fluidically couple the feed port and the networkport when in a first rotational position and fluidically couple the feedport and the reservoir port when in a second rotational position.

In another aspect, the mating side of a removable cartridge set forthherein may be a first mating side and the removable cartridge mayinclude a second mating side. The first and second mating sides face inopposite directions. The second mating side is configured to engage theinstrument mechanically, fluidically, or thermally.

In an embodiment, a base instrument is provided that includes a systemhousing having a control side that is configured to engage a removablecartridge. The base instrument also includes a rotating motor that isconfigured to engage a rotatable valve of the removable cartridge. Thebase instrument also includes an actuator that is configured to engage achannel valve of the removable cartridge and an array of electricalcontacts configured to electrically couple to the removable cartridge.The base instrument also includes a system controller that is configuredto control the rotating motor and the actuator to perform an assayprotocol within the removable cartridge. The system controller isconfigured to receive imaging data from the removable cartridge throughthe array of electrical contacts. Optionally, the base instrumentincludes a thermal block for heating a portion of the removablecartridge.

In an embodiment, a removable cartridge is provided that includes acartridge housing having a sample port that opens to an exterior of thecartridge housing and is configured to receive a biological sample. Thecartridge housing includes a mating side that is configured to face andremovably couple to a base instrument. The removable cartridge alsoincludes a microfluidic body disposed within the cartridge housing. Themicrofluidic body has a body side and includes a fluidic network. Thefluidic network has a plurality of discrete channels and correspondingports that open at the body side at a valve-receiving area. Theremovable cartridge also includes a rotatable valve disposed within thecartridge housing. The rotatable valve has a fluidic side and at leastone flow channel that extends between a plurality of valve ports. Thevalve ports open to the fluidic side. The fluidic side is rotatablycoupled to the valve-receiving area of the body side of the microfluidicbody, wherein the rotatable valve is movable between differentrotational positions to fluidically couple the discrete channels. Therotatable valve has a mechanical interface that is accessible along themating side and configured to engage the base instrument such that therotatable valve is controlled by the base instrument.

In an embodiment, a removable cartridge is provided that includes acartridge housing having a sample port that opens to an exterior of thecartridge housing and is configured to receive a biological sample. Thecartridge housing has a mating side that is configured to removablycouple to a base instrument. The removable cartridge also includes amicrofluidic structure that is disposed within the cartridge housing andincludes a plurality of stacked printed circuit board (PCB) layers. ThePCB layers includes fluidic layers that define channels and a reactionchamber when the PCB layers are stacked. The PCB layers also include awiring layer. The removable cartridge also includes a CMOS imager thatis configured to be mounted to the microfluidic structure andelectrically coupled to the wiring layer. The CMOS imager is oriented todetect designated reactions within the reaction chamber.

In one aspect, the removable cartridge includes input/output (I/O)contacts that are exposed to an exterior of the cartridge housing. TheI/O contacts may be electrically coupled to the CMOS imager.

In one aspect, the microfluidic structure of a removable cartridge setforth herein includes a channel valve in which at least a portion of thechannel valve is defined by the PCB layers. The channel valve isconfigured to be actuated to block and permit flow through one of thechannels.

As used herein, an element or step recited in the singular and proceededwith the word “a” or “an” should be understood as not excluding pluralof said elements or steps, unless such exclusion is explicitly stated.Furthermore, references to “one embodiment” are not intended to beinterpreted as excluding the existence of additional embodiments thatalso incorporate the recited features. Moreover, unless explicitlystated to the contrary, embodiments “comprising” or “having” an elementor a plurality of elements having a particular property may includeadditional elements whether or not they have that property.

It should be noted that the particular arrangement of components (e.g.,the number, types, placement, or the like) of the illustratedembodiments may be modified in various alternate embodiments. In variousembodiments, different numbers of a given module or unit may beemployed, a different type or types of a given module or unit may beemployed, a given module or unit may be added, or a given module or unitmay be omitted.

It is to be understood that the above description is intended to beillustrative, and not restrictive. For example, the above-describedembodiments (and/or aspects thereof) may be used in combination witheach other. In addition, many modifications may be made to adapt aparticular situation or material to the teachings of the variousembodiments without departing from its scope. Dimensions, types ofmaterials, orientations of the various components, and the number andpositions of the various components described herein are intended todefine parameters of certain embodiments, and are by no means limitingand are merely exemplary embodiments. Many other embodiments andmodifications within the spirit and scope of the claims will be apparentto those of skill in the art upon reviewing the above description. Thepatentable scope should, therefore, be determined with reference to theappended claims, along with the full scope of equivalents to which suchclaims are entitled.

As used in the description, the phrase “in an exemplary embodiment” andthe like means that the described embodiment is just one example. Thephrase is not intended to limit the inventive subject matter to thatembodiment. Other embodiments of the inventive subject matter may notinclude the recited feature or structure. In the appended claims, theterms “including” and “in which” are used as the plain-Englishequivalents of the respective terms “comprising” and “wherein.”Moreover, in the following claims, the terms “first,” “second,” and“third,” etc. are used merely as labels, and are not intended to imposenumerical requirements on their objects. Further, the limitations of thefollowing claims are not written in means—plus-function format and arenot intended to be interpreted based on 35 U.S.C. § 112(f), unless anduntil such claim limitations expressly use the phrase “means for”followed by a statement of function void of further structure.

What is claimed is:
 1. A removable cartridge comprising: a cartridgehousing having a sample port that opens to an exterior of the cartridgehousing and is configured to receive a biological sample, the cartridgehousing has an exterior side that is configured to engage a baseinstrument; a rotatable valve disposed within the cartridge housing, therotatable valve having a fluidic side and a plurality of valve portsthat open at the fluidic side, the rotatable valve having at least oneflow channel extending between the valve ports, wherein the rotatablevalve is rotatable between different rotational positions; amicrofluidic body having a body side that is slidably coupled to thefluidic side of the rotatable valve, the microfluidic body at leastpartially defining a fluidic network that includes: a sample channel inflow communication with the sample port, the sample channel having anetwork port that opens to the body side of the microfluidic body; areservoir configured to hold a reagent, the reservoir being in flowcommunication with a reservoir port that opens to the fluidic side ofthe microfluidic body; and a feed channel in flow communication with areaction chamber of the fluidic network, the feed channel having a feedport that opens to the body side of the microfluidic body; wherein therotatable valve is configured to rotate between first and secondrotational positions, the network port being fluidically coupled to thefeed port through the rotatable valve when the rotatable valve is in thefirst rotational position, the reservoir port being fluidically coupledto the feed port through the rotatable valve when the rotatable valve isin the second rotational position.
 2. The removable cartridge of claim1, wherein the rotatable valve including a mechanical interface that isaccessible at the exterior side and configured to engage the baseinstrument.
 3. The removable cartridge of claim 1, wherein the storagemodule includes reagents for conducting a sequencing-by-synthesis (SBS)protocol.
 4. The removable cartridge of claim 1, wherein the rotatablevalve in the first rotational position is configured to receive a sampleliquid when a force on the fluid moves the sample liquid toward the feedport, wherein the rotatable valve in the second rotational position isconfigured to allow the sample liquid to be displaced into the reservoirwhen a displacement force pushes the sample liquid away from the feedport into the reservoir.
 5. The removable cartridge of claim 1, whereinthe rotatable valve rotates about an axis, the feed port being alignedwith the axis.
 6. A removable cartridge comprising: a cartridge housinghaving a sample port that opens to an exterior of the cartridge housingand is configured to receive a biological sample, the cartridge housingincluding a mating side configured to face and removably couple to abase instrument; a fluidic network disposed within the housing, thefluidic network including a sample channel that is in flow communicationwith the sample port; a channel valve including a flex member configuredto move between first and second positions, the flex member blockingflow through the sample channel when in the first position andpermitting flow through the sample channel when in the second position,wherein the mating side of the cartridge housing includes an accessopening that exposes the channel valve to the exterior of the cartridgehousing, the access opening configured to receive a valve actuator ofthe base instrument for moving the flex member between the first andsecond positions.
 7. The removable cartridge of claim 6, wherein theflex member comprises a flexible layer that covers an interior cavity ofthe fluidic network, the flexible layer configured to be pushed into thecavity to block flow therethrough.
 8. The removable cartridge of claim6, further comprising a rotatable valve disposed within the cartridgehousing, the rotatable valve configured to rotate between differentpositions to change a flow path of the fluidic network, the rotatablevalve including a mechanical interface that is operably accessible alongthe mating side.
 9. The removable cartridge of claim 6, wherein thefluidic network includes a network port in flow communication with thesample channel, a feed port in flow communication with a reactionchamber, and a reservoir port in flow communication with a reservoirthat is configured to store a reagent, the removable cartridge furthercomprising a rotatable valve disposed within the cartridge housing, therotatable valve fluidically coupling the feed port and the network portwhen in a first rotational position and fluidically coupling the feedport and the reservoir port when in a second rotational position. 10.The removable cartridge of claim 6, wherein the mating side is a firstmating side and the removable cartridge includes a second mating side,the first and second mating sides facing in opposite directions, thesecond mating side configured to engage the instrument mechanically,fluidically, or thermally.